Systems, methods, and interfaces for identifying effective electrodes

ABSTRACT

Systems, methods, and interfaces are described herein for identification of effective electrodes to be used in sensing and/or therapy. Two or more portions of a signal monitored using an electrode may be compared to determine whether the electrode is effective. The two or more portions may correspond to the same portion or window of a cardiac cycle. Further, signals from a first electrode and from a second electrode located proximate the first electrode may be compared to determine whether one or both of the electrodes are effective.

CROSS-REFERENCE TO RELATED APPLICATION

This application claims the benefit of U.S. Provisional PatentApplication 61/913,795 entitled “Systems, Methods, and Interfaces forIdentifying Effective Electrodes” and filed on Dec. 9, 2013 and U.S.Provisional Patent Application 61/817,483 entitled “IdentifyingEffective Electrodes” and filed on Apr. 30, 2013, each of which isincorporated herein by reference in its entirety.

BACKGROUND

The disclosure herein relates to systems, methods, and interfaces foridentifying effective electrodes used to sense signals from tissueand/or deliver therapy to tissue. The identified electrodes may be usedin systems, methods, and interfaces for navigating an implantableelectrode to a region of a patient's heart for cardiac therapy.

Electrodes may be used in various systems, devices, and methods formedical treatment of a patient. More specifically, electrodes may belocated adjacent, or in contact, with tissue (e.g., skin, cardiactissue, etc.) of a patient to sense signals from the tissue of thepatient and/or deliver therapy to the tissue of the patient. Each of theelectrodes may be effective or ineffective for sensing signals from thetissue of the patient and/or delivering therapy to the tissue of thepatient for multiple reasons. For example, an electrode may not beeffectively coupled to, or in contact with, the tissue of the patientrendering the electrode ineffective for sensing signals form the tissueof the patient and/or delivering therapy to the tissue of the patient.Further, for example, an electrode, or an electrical connection betweenthe electrode and monitoring apparatus, may be damaged or otherwisenon-functional rendering the electrode ineffective for sensing signalsfrom the tissue of the patient and/or delivering therapy to the tissueof the patient.

Exemplary apparatus that utilize multiple electrodes may includemultipolar catheters (e.g., catheters including multiple electrodes,etc.) configured to record activation times/voltage mappingsimultaneously at different points along a coronary sinus vein or someother anatomic structure (e.g., used for electrical mapping). Further,exemplary apparatus may include multi-electrode electrocardiogram (ECG)systems for body-surface potential mapping configured to recordsimultaneous ECG measurements from multiple electrodes.

SUMMARY

The exemplary systems, apparatus, and methods described herein may beconfigured to analyze one or more signals from one or more electrodesand evaluate the one or more signals to determine whether the one ormore electrodes are effective for sensing signals and/or deliveringtherapy.

An exemplary system for identifying effective electrodes may includeelectrode apparatus and computing apparatus. The electrode apparatus mayinclude a plurality of electrodes (e.g., surface electrodes positionedin an array) configured to be located proximate tissue of a patient. Thecomputing apparatus may be coupled to the electrode apparatus forsensing electrical activity using the electrode apparatus and may beconfigured to perform an effectiveness test for each electrode of theplurality of electrodes resulting in an effectiveness value (e.g., aPearson correlation coefficient) for each electrode. To perform theeffectiveness test for each electrode, the computing apparatus may befurther configured to monitor a signal from the patient using anelectrode, store a portion of the signal over a preset time period(e.g., less than or equal to 250 milliseconds) for each cardiac cycle ofat least two cardiac cycles (e.g. storing the portion of the signalbased on a recurring fiducial element within a cardiac signal), whereeach portion corresponds to the same time frame within each cardiaccycle, and compare at least two stored portions of the signal to providethe effectiveness value representative of the effectiveness of theelectrode for sensing signals from the tissue of the patient.

An exemplary method for identifying effective electrodes in a pluralityof electrodes (e.g., surface electrodes positioned in an array) locatedproximate tissue of a patient may include monitoring a signal from thepatient using an electrode, storing a portion of the signal over apreset time period (e.g., less than or equal to 250 milliseconds) foreach cardiac cycle of at least two cardiac cycles (e.g. storing theportion of the signal based on a recurring fiducial element within acardiac signal), where each portion corresponds to the same time framewithin each cardiac cycle, and comparing at least two stored portions ofthe signal to provide an effectiveness value (e.g., a Pearsoncorrelation coefficient) representative of the effectiveness of theelectrode for sensing signals from the tissue of the patient.

An exemplary system for identifying effective electrodes may includeelectrode means for monitoring a signal from the patient and computingmeans for storing a portion of the signal over a preset time period foreach cardiac cycle of at least two cardiac cycles. Each portion maycorrespond to the same time frame within each cardiac cycle. Thecomputing means may be further for comparing at least two storedportions of the signal to provide an effectiveness value representativeof the effectiveness of the electrode for sensing signals from thetissue of the patient.

An exemplary system for use in cardiac therapy may include electrodeapparatus (e.g., a plurality of electrodes configured to be locatedproximate tissue of a patient), display apparatus including a graphicaluser interface (e.g., the graphical user interface may be configured topresent information for use in assisting a user in at least one ofassessing a patient's cardiac health, evaluating adjusting cardiactherapy delivered to a patient, and navigating at least one implantableelectrode to a region of the patient's heart (e.g., graphically depictat least a portion of anatomy, such as blood vessel anatomy, of thepatient's heart for use in assisting a user in navigating at least oneimplantable electrode to a region of the patient's heart, etc.), andcomputing apparatus coupled to the electrode apparatus and displayapparatus. The computing apparatus may be configured to perform aneffectiveness test for each electrode of the plurality of electrodesresulting in an effectiveness value for each electrode. To perform theeffectiveness test for each electrode, the computing apparatus may befurther configured to monitor a signal from the patient using anelectrode and store a portion of the signal over a preset time periodfor each cardiac cycle of at least two cardiac cycles. Each portion maycorrespond to the same time frame within each cardiac cycle. Thecomputing apparatus may be further configured to compare at least twostored portions of the signal to provide the effectiveness valuerepresentative of the effectiveness of the electrode for sensing signalsfrom the tissue of the patient. The computing apparatus may be furtherconfigured to display, on the graphical user interface, information foruse in assisting a user in at least one of assessing a patient's cardiachealth, evaluating and adjusting cardiac therapy delivered to a patient,and navigating at least one implantable electrode to a region of thepatient's heart (e.g., at least a portion of anatomy, such as bloodvessel anatomy, of the patient's heart for use in assisting a user innavigating at least one implantable electrode to a region of thepatient's heart, etc.).

An exemplary method for use in cardiac therapy may include monitoring asignal from the patient using an electrode and storing a portion of thesignal over a preset time period for each cardiac cycle of at least twocardiac cycles, each portion corresponds to the same time frame withineach cardiac cycle. The exemplary method may further include comparingat least two stored portions of the signal to provide an effectivenessvalue representative of the effectiveness of the electrode for sensingsignals from the tissue of the patient and displaying, on a graphicaluser interface, information for use in assisting a user in at least oneof assessing a patient's cardiac health, evaluating and adjustingcardiac therapy delivered to a patient, and navigating at least oneimplantable electrode to a region of the patient's heart (e.g., at leasta portion of anatomy of the patient's heart for use in assisting a userin navigating at least one implantable electrode to a region of thepatient's heart, etc.).

An exemplary system for use in cardiac therapy may include electrodemeans for monitoring a signal from the patient and computing means forstoring a portion of the signal over a preset time period for eachcardiac cycle of at least two cardiac cycles. Each portion maycorrespond to the same time frame within each cardiac cycle. Thecomputing means may be further for comparing at least two storedportions of the signal to provide an effectiveness value representativeof the effectiveness of the electrode for sensing signals from thetissue of the patient. The exemplary system may further include displaymeans for displaying, on a graphical user interface, information for usein assisting a user in at least one of assessing a patient's cardiachealth, evaluating and adjusting cardiac therapy delivered to a patient,and navigating at least one implantable electrode to a region of thepatient's heart (e.g., at least a portion of anatomy, such as bloodvessel anatomy, of the patient's heart for use in assisting a user innavigating at least one implantable electrode to a region of thepatient's heart, etc.).

In one or more embodiments, the effectiveness value may include acorrelation value, the computing apparatus may be further configured toexecute or the method may further include disabling any electrode of theplurality of electrodes having a correlation value less than a selectedthreshold value (e.g., greater than or equal to 0.7 and less than orequal to about 0.95). In one or more embodiments, the effectivenessvalue may include a correlation value, the computing apparatus may befurther configured to execute or the method may further include enablingany electrode of the plurality of electrodes having a correlation valuegreater than or equal to a selected threshold value.

In one or more embodiments, the computing apparatus may be furtherconfigured to execute or the method may further include performing anadditional effectiveness test for each electrode of the plurality ofelectrodes resulting in another correlation value for each electrode ifmore than a selected percentage of the plurality of electrodes had acorrelation value less than a selected threshold value. In one or moreembodiments, the computing apparatus may be further configured toexecute or the method may further include aligning the at least twoportions of the signal prior to the comparison.

One exemplary system for identifying effective electrodes may includeelectrode apparatus and computing apparatus. The electrode apparatus mayinclude a plurality of electrodes (e.g., surface electrodes positionedin an array) configured to be located proximate tissue of a patient. Thecomputing apparatus may be coupled to the electrode apparatus forsensing electrical activity using the electrode apparatus and may beconfigured to perform an effectiveness test for each electrode of theplurality of electrodes resulting in an effectiveness value (e.g.,representing a correlation value between the primary electrode and oneneighbor electrode, a Pearson correlation coefficient, etc.) for eachelectrode. To perform the effectiveness test for each electrode, thecomputing apparatus may be further configured to monitor a first signalfrom the patient using a primary electrode and monitor at least onesecondary signal from the patient using at least one neighbor electrode.At least one neighbor electrode may be spatially adjacent to the primaryelectrode (e.g., within 3 centimeters from the primary electrode). Thecomputing apparatus may be further configured to store a portion of thefirst signal over a time period (e.g., corresponding to ventriculardepolarization, less than or equal to 250 milliseconds, etc.), store aportion of each of the at least one secondary signal over the timeperiod, and compare the portion of the first signal to the portion ofeach of the at least one secondary signal to provide at least oneeffectiveness value representative of the effectiveness of the electrodefor sensing cardiac signals from the tissue of the patient.

One exemplary method for identifying effective electrodes (e.g., surfaceelectrodes positioned in an array) may include monitoring a first signalfrom a patient using a primary electrode and monitoring at least onesecondary signal from the patient using at least one neighbor electrode.At least one neighbor electrode may be spatially adjacent to the primaryelectrode (e.g., within 3 centimeters from the primary electrode). Theexemplary method may further include storing a portion of the firstsignal over a time period (e.g., corresponding to ventriculardepolarization, less than or equal to 250 milliseconds, etc.), storing aportion of each of the at least one secondary signal over the timeperiod, and comparing the portion of the first signal to the portion ofeach of the at least one secondary signal to provide at least oneeffectiveness value (e.g., representing a correlation value between theprimary electrode and one neighbor electrode, a Pearson correlationcoefficient, etc.) representative of the effectiveness of the electrodefor sensing cardiac signals from the tissue of the patient.

An exemplary system for identifying effective electrodes may includeelectrode means for monitoring a first signal from a patient using aprimary electrode and for monitoring at least one secondary signal fromthe patient using at least one neighbor electrode, where the at leastone neighbor electrode is spatially adjacent to the primary electrode,and computing means for storing a portion of the first signal over atime period, for storing a portion of each of the at least one secondarysignal over the time period, and for comparing the portion of the firstsignal to the portion of each of the at least one secondary signal toprovide at least one effectiveness value representative of theeffectiveness of the electrode for sensing cardiac signals from thetissue of the patient.

An exemplary system for use in cardiac therapy may include electrodeapparatus (e.g., a plurality of electrodes configured to be locatedproximate tissue of a patient) and display apparatus including agraphical user interface (e.g., the graphical user interface may beconfigured to present information for use in assisting a user in atleast one of assessing a patient's cardiac health, evaluating andadjusting cardiac therapy delivered to a patient, and navigating atleast one implantable electrode to a region of the patient's heart(e.g., graphically depict at least a portion of anatomy, such as bloodvessel anatomy, of the patient's heart for use in assisting a user innavigating at least one implantable electrode to a region of thepatient's heart, etc.). The exemplary system may further includecomputing apparatus coupled to the electrode apparatus and displayapparatus. The computing apparatus may be configured to perform aneffectiveness test for each electrode of the plurality of electrodesresulting in an effectiveness value for each electrode. To perform theeffectiveness test for each electrode, the computing apparatus may befurther configured to monitor a first signal from the patient using aprimary electrode, monitor at least one secondary signal from thepatient using at least one neighbor electrode, where the at least oneneighbor electrode is spatially adjacent to the primary electrode, storea portion of the first signal over a time period, and store a portion ofeach of the at least one secondary signal over the time period. Thecomputing apparatus may be further configured to compare the portion ofthe first signal to the portion of each of the at least one secondarysignal to provide at least one effectiveness value representative of theeffectiveness of the electrode for sensing cardiac signals from thetissue of the patient and display, on the graphical user interface,information for use in assisting a user in at least one of assessing apatient's cardiac health, evaluating and adjusting cardiac therapydelivered to a patient, and navigating at least one implantableelectrode to a region of the patient's heart (e.g., at least a portionof anatomy, such as blood vessel anatomy, of the patient's heart for usein assisting a user in navigating at least one implantable electrode toa region of the patient's heart, etc.).

An exemplary method for use in cardiac therapy may include monitoring afirst signal from a patient using a primary electrode and monitoring atleast one secondary signal from the patient using at least one neighborelectrode, where the at least one neighbor electrode is spatiallyadjacent to the primary electrode. The exemplary method may furtherinclude storing a portion of the first signal over a time period,storing a portion of each of the at least one secondary signal over thetime period, and comparing the portion of the first signal to theportion of each of the at least one secondary signal to provide at leastone effectiveness value representative of the effectiveness of theelectrode for sensing cardiac signals from the tissue of the patient.The exemplary method may further include displaying, on a graphical userinterface, information for use in assisting a user in at least one ofassessing a patient's cardiac health, evaluating and adjusting cardiactherapy delivered to a patient, and navigating at least one implantableelectrode to a region of the patient's heart (e.g., at least a portionof anatomy, such as blood vessel anatomy, of the patient's heart for usein assisting a user in navigating at least one implantable electrode toa region of the patient's heart, etc.).

An exemplary system for use in cardiac therapy may include electrodemeans for monitoring a first signal from a patient using a primaryelectrode and for monitoring at least one secondary signal from thepatient using at least one neighbor electrode, where the at least oneneighbor electrode is spatially adjacent to the primary electrode, andcomputing means for storing a portion of the first signal over a timeperiod, for storing a portion of each of the at least one secondarysignal over the time period, and for comparing the portion of the firstsignal to the portion of each of the at least one secondary signal toprovide at least one effectiveness value representative of theeffectiveness of the electrode for sensing cardiac signals from thetissue of the patient. The exemplary system may further include displaymeans for displaying, on a graphical user interface, information for usein assisting a user in at least one of assessing a patient's cardiachealth, evaluating and adjusting cardiac therapy delivered to a patient,and navigating at least one implantable electrode to a region of thepatient's heart (e.g., at least a portion of anatomy, such as bloodvessel anatomy, of the patient's heart for use in assisting a user innavigating at least one implantable electrode to a region of thepatient's heart, etc.).

In one or more embodiments, the effectiveness value may include acorrelation value, and the computing apparatus may be further configuredto execute or the method may further include disabling any electrode ofthe plurality of electrodes having all of their at least one correlationvalue less than or equal to a selected threshold value (e.g., greaterthan or equal to 0.7 and less than or equal to about 0.95).

In one or more embodiments, the computing apparatus may be furtherconfigured to execute or the method may further include performing anadditional effectiveness test for each electrode of the plurality ofelectrodes resulting in at least one additional correlation value foreach electrode if more than a selected percentage of the plurality ofelectrodes had all of their at least one correlation value less than aselected threshold value.

In one or more embodiments, the computing apparatus may be furtherconfigured to execute or the method may further include generating agraphical map including the plurality of electrodes spatiallydistributed and the effectiveness values of the plurality of electrodes.

One exemplary system for identifying effective electrodes may includeelectrode apparatus and computing apparatus. The electrode apparatus mayinclude a plurality of electrodes configured to be located proximatetissue of a patient. The computing apparatus may be coupled to theelectrode apparatus for sensing electrical activity using the electrodeapparatus and may be configured to perform an effectiveness test foreach electrode of the plurality of electrodes resulting in aneffectiveness value for each electrode. To perform the effectivenesstest for each electrode, the computing apparatus may be furtherconfigured to monitor a signal from the patient using an electrode,store a portion of the signal over a preset time period, and compare atleast one morphological feature of the portion of the signal to at leastone physiological indication value to provide the effectiveness valuerepresentative of the effectiveness of the electrode for sensing signalsfrom the tissue of the patient. In at least one embodiment, the at leastone morphological feature may include at least one of maximum value,minimum value, difference between maximum and minimum value, maximumslope, minimum slope, and difference between maximum slope and minimumslope.

In at least one embodiment, the system or method may be configured tocompare morphologic similarity of a signal recorded at an electrodewithin an electrode array with that of its spatially adjacent neighborelectrodes, e.g., using a Pearson correlation coefficient or a waveformmatch percentage, etc. The largest value of correlation coefficient orwaveform match percentage or the “best match” value of these or similarmetrics (e.g., value(s), functions, comparisons, differences, averages,slopes, etc.) may be selected and the process may be repeated for eachelectrode in the array to find the “best match” value for eachelectrode. Then, electrodes may be selected to be used (e.g., forfurther analysis) based on whose “best match” value exceeds a certainthreshold (e.g., a correlation coefficient greater than or equal to 0.8and/or a waveform match percentage score greater than 70). In essence,valid cardiac signals from an electrode within a spatial electrode-arraymay bear a high degree of similarity with signals from at least one ofthe neighbor electrodes whereas non-physiological signals (e.g., noise)may be uncorrelated with signals monitored by neighbor electrodes (e.g.,valid cardiac signals, noise, etc.).

One exemplary method relates to time correlation of beats sensed fromone electrode and includes picking a timing fiducial element (e.g., aV-s or VP marker, a dominant peak or valley on a given ECG lead, etc.)corresponding to each beat, generating a window over a signal of eachbeat at each electrode about the fiducial, computing a correlationbetween the windowed signals at each electrode for beats j and j−1, andfinding all electrodes which yield a correlation less than or equal to0.8. In at least one embodiment, the method includes determining if anumber of electrodes with a correlation less than or equal to 0.8exceeds N/2 (where N is the number of electrodes), and if not,eliminating electrodes with correlation less than or equal to 8 andperforming analysis with remaining electrodes for beats j and j−1.Further, if the electrodes are within the correlation, then skip beats jand j−1 and move on to the next pair of beats (j, j+1) to repeatanalysis and/or adjust electrode positions. The exemplary method may berepeated for each electrode of the N electrodes.

One exemplary method may include comparing morphologic similarity ofsignals recorded at an electrode within an N array (e.g., 6 or 7electrodes, 2 or more electrodes, etc.) with that of its spatiallyadjacent neighbors. The morphologic comparison may employ the Pearsoncorrelation coefficient, waveform match percentage, and/or any number ofmethods. The method further includes selecting the largest value ofcorrelation coefficient or waveform match percentage or the ‘best match’value of these or similar metrics (e.g., value(s), functions,comparisons, differences, averages, slopes, etc.), repeating for eachelectrode in the array and finding the ‘best match’ value of thatelectrode, and selecting signals (e.g., for further analysis) fromelectrodes in which the ‘best match’ value exceeds a certain threshold(e.g., a correlation coefficient greater than 0.8 or waveform matchpercentage score greater than 70).

One exemplary apparatus for automatically selecting electrodes from asurface electrode-array for CRT implant feedback (e.g., evaluatingelectrical dyssynchrony of the heart of a patient) may include sensingmeans for sensing a signal from a first one of surface electrode-arrayin response to the ventricular pacing stimulus, storing means forstoring the first sensed signal, sensing means for sensing a secondsignal from a second one of surface electrode-array in response to theventricular pacing stimulus, storing means for storing the second sensedsignal, processing means for comparing morphologic features between thefirst and second signals, determining means for determining similarityof the morphological features between the first and second signals, andmeans for repeatedly processing each electrode of the surface electrodearray. Further, the processing means may be configured for determininggreatest similarity of the morphological features between two adjacentelectrodes of the surface electrode array. The exemplary apparatus mayfurther include selecting means for selecting two adjacent electrodesthat exhibit the greatest similarity of the morphological featuresfollowing the repeated operations for each electrode of the surfaceelectrode array, wherein the selecting means is performed withoutprocessing data related to intraventricular synchrony.

The above summary is not intended to describe each embodiment or everyimplementation of the present disclosure. A more complete understandingwill become apparent and appreciated by referring to the followingdetailed description and claims taken in conjunction with theaccompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagram of an exemplary system including an exemplaryimplantable medical device (IMD).

FIG. 2A is a diagram of the exemplary IMD of FIG. 1.

FIG. 2B is a diagram of an enlarged view of a distal end of theelectrical lead disposed in the left ventricle of FIG. 2A.

FIG. 3A is a block diagram of an exemplary IMD, e.g., the IMD of FIGS.1-2.

FIG. 3B is another block diagram of an exemplary IMD (e.g., animplantable pulse generator) circuitry and associated leads employed inthe system of FIGS. 1-2 for providing three sensing channels andcorresponding pacing channels.

FIG. 4 is a diagram of an exemplary system including electrodeapparatus, imaging apparatus, display apparatus, and computingapparatus.

FIGS. 5A-5B are conceptual diagrams illustrating exemplary systems formeasuring torso-surface potentials.

FIG. 6 is a block diagram of an exemplary method of identifying aneffective electrode using single signal correlation.

FIG. 7 is a block diagram of an exemplary method of identifying one ormore effective electrodes using single signal correlation.

FIG. 8 is a diagram of an exemplary electrode array.

FIG. 9 is a block diagram of an exemplary method of identifying aneffective electrode using spatial signal correlation, e.g. using theelectrode array of FIG. 8.

FIG. 10 depicts a graph depicting correlation values for a plurality ofelectrodes.

FIG. 11 depicts three graphs depicting signals for ineffectiveelectrodes.

FIG. 12 depicts two graphs depicting signals for effective electrodes.

FIG. 13 depicts a graph of a distribution of correlation values for aplurality of electrodes evaluated by, e.g., the exemplary methods ofFIGS. 6-7 and 9.

FIG. 14 is a block diagram of an exemplary method of identifying aneffective electrode using morphological features.

FIG. 15 is an exemplary graphical user interface depicting blood vesselanatomy configured to assist a user in navigating an implantableelectrode to a region of a patient's heart for cardiac therapy.

FIG. 16 is an exemplary graphical user interface depicting a human heartincluding activation times mapped thereon configured to assist a user innavigating an implantable electrode to a region of a patient's heart forcardiac therapy.

DETAILED DESCRIPTION OF EXEMPLARY EMBODIMENTS

In the following detailed description of illustrative embodiments,reference is made to the accompanying figures of the drawing which forma part hereof, and in which are shown, by way of illustration, specificembodiments which may be practiced. It is to be understood that otherembodiments may be utilized and structural changes may be made withoutdeparting from (e.g., still falling within) the scope of the disclosurepresented hereby.

Exemplary systems, apparatus, and methods shall be described withreference to FIGS. 1-16. It will be apparent to one skilled in the artthat elements or processes from one embodiment may be used incombination with elements or processes of the other embodiments, andthat the possible embodiments of such methods, apparatus, and systemsusing combinations of features set forth herein is not limited to thespecific embodiments shown in the Figures and/or described herein.Further, it will be recognized that the embodiments described herein mayinclude many elements that are not necessarily shown to scale. Stillfurther, it will be recognized that timing of the processes and the sizeand shape of various elements herein may be modified but still fallwithin the scope of the present disclosure, although certain timings,one or more shapes and/or sizes, or types of elements, may beadvantageous over others.

As described herein, various exemplary systems, apparatus, and methodsmay utilize electrodes configured to sense one or more signals fromtissue of a patient and/or deliver therapy to tissue of the patient. Forexample, electrodes may be included in apparatus such as vests, bands,belts, straps, patches, any wearable garment, t-shirts, bras, hats(e.g., for neural signals), etc. and may be configured to be locatedexternally to the patient in contact with the skin of the patient for,e.g., monitoring cardiac signals (e.g., electrocardiograms) of apatient, mapping a patient's heart, etc. Further, for example,electrodes may be individually located, or placed, on a patient.Further, for example, electrodes may be included in or on apparatus suchas a basket catheter, a sock, etc., and may be configured to be locatedwithin internal spaces (e.g., cardiac spaces) of a patient, e.g., forcardiac mapping purposes, etc. Further, for example, electrodes may beincluded as part of an implantable medical device (IMD) and located onone or more leads configured to be located proximate one or moreportions of a patient's heart.

In at least one embodiment, a spatial surface electrode array configuredto record cardiac signals for computing indices related to electricaldyssynchrony and ventricular activation (which, e.g., may be useful asfeedback for cardiac resynchronization therapy implant) may be used.Further, metrics computed from signals from the electrode arrays may beused to, e.g., estimate the time of delivery of left ventricular pacingfor optimal fusion for left ventricular-only fusion pacing (e.g.,adaptive cardiac resynchronization therapy), estimate scar-burden, etc.

As described herein, various exemplary systems, apparatus, and methodsmay utilize electrodes configured for any kind of cardiac mapping gride.g., a sock of electrodes to map electrical activity on the outersurface of the heart, a basket or constellation catheter to mapelectrical activity within a chamber or the endocardial wall, multipolarleads to map electrical activity of the heart or within a vein in theheart, multi-electrode catheters used for mapping, etc.

Electrodes may be effective or ineffective for sensing signals and/ordelivering therapy depending on multiple factors such as whether theelectrodes are properly located, whether the electrodes are insufficient contact with tissue, whether the electrodes or theconnections to the electrodes are damaged, etc. As such, a practicalproblem with a multi-electrode array may be that some of the electrodesmay not be effective, and thus, may not provide valid signals (e.g.,valid cardiac signals, signals having an adequate signal-to-noise ratio,etc.).

The exemplary systems, apparatus, and methods described herein mayprovide a way of automated selection of effective electrodes, orelectrodes with valid signals, with little error and/or with minimumoperator input. The exemplary systems, apparatus, and methods mayprovide automated selection of effective electrodes based onsimilarities, or correlations, of a portion, or window, of a signal foran electrode for a cardiac cycle with another portion of the signal forthe electrode for another cardiac cycle. Further, the exemplary systems,apparatus, and methods may provide automated selection of effectiveelectrodes based on similarities, or correlations, of a signal of anelectrode with a signal of the spatially adjacent neighbor electrode(s).The automated identification of effective electrodes (e.g., capable ofsensing valid cardiac signals) and exclusion of electrodes with noisemay provide subsequent analysis with signals from the array that isaccurate and provides correct assessment of the electrical dyssynchronyof the heart of a patient that may facilitate patient selection for CRT,facilitate placement of implantable leads (e.g., one or more leftventricular leads) and programming of device parameters for CRT duringan implantation procedure, reprogramming of device parameters for CRTduring a follow-up visit, etc. For example, a user may make a diagnosis,prescribe CRT, position therapy devices, e.g., leads, or adjust orselect treatment parameters based on the indicated electricaldyssynchrony.

The exemplary methods and processes described herein may be utilized andimplemented by one or more (e.g., two or more, a plurality, etc.)systems, apparatus, and devices that include and/or are coupled to atleast one electrode. For example, the exemplary methods and processesmay be used by an exemplary therapy system 10 described herein withreference to FIGS. 1-3 and exemplary sensing systems 110, 111 includinga spatial electrode-array as described herein with reference to FIGS.5A-5B. Although only therapy system 10 and sensing systems 110, 111 aredescribed and depicted herein, it is to be understood that the exemplarymethods and processes may be used by any system including computingapparatus capable of analyzing signals from one or more electrodes. Thecomputing apparatus, for example, may be located in an external computeror programmer, may be located in an IMD, or may be located on a serverattached to a network.

FIG. 1 is a conceptual diagram illustrating an exemplary therapy system10 that may be used to deliver pacing therapy to a patient 14. Patient14 may, but not necessarily, be a human. The therapy system 10 mayinclude an implantable medical device 16 (IMD), which may be coupled toleads 18, 20, 22 and/or a programmer 24. The IMD 16 may be, e.g., animplantable pacemaker, cardioverter, and/or defibrillator, that provideselectrical signals to the heart 12 of the patient 14 via electrodescoupled to one or more of the leads 18, 20, 22.

The leads 18, 20, 22 extend into the heart 12 of the patient 14 to senseelectrical activity of the heart 12 and/or to deliver electricalstimulation to the heart 12. In the example shown in FIG. 1, the rightventricular (RV) lead 18 extends through one or more veins (not shown),the superior vena cava (not shown), and the right atrium 26, and intothe right ventricle 28. The left ventricular (LV) coronary sinus lead 20extends through one or more veins, the vena cava, the right atrium 26,and into the coronary sinus 30 to a region adjacent to the free wall ofthe left ventricle 32 of the heart 12. The right atrial (RA) lead 22extends through one or more veins and the vena cava, and into the rightatrium 26 of the heart 12.

The IMD 16 may sense, among other things, electrical signals attendantto the depolarization and repolarization of the heart 12 via electrodescoupled to at least one of the leads 18, 20, 22. The IMD 16 may beconfigured to determine or identify effective electrodes located on theleads 18, 20, 22 using the exemplary methods and processes describedherein. In some examples, the IMD 16 provides pacing therapy (e.g.,pacing pulses) to the heart 12 based on the electrical signals sensedwithin the heart 12. The IMD 16 may be operable to adjust one or moreparameters associated with the pacing therapy such as, e.g., AV delayand other various timings, pulse width, amplitude, voltage, burstlength, etc. Further, the IMD 16 may be operable to use variouselectrode configurations to deliver pacing therapy, which may beunipolar, bipolar, quadripoloar, or further multipolar. For example, amultipolar lead may include several electrodes which can be used fordelivering pacing therapy. Hence, a multipolar lead system may provide,or offer, multiple electrical vectors to pace from. A pacing vector mayinclude at least one cathode, which may be at least one electrodelocated on at least one lead, and at least one anode, which may be atleast one electrode located on at least one lead (e.g., the same lead,or a different lead) and/or on the casing, or can, of the IMD. Whileimprovement in cardiac function as a result of the pacing therapy mayprimarily depend on the cathode, the electrical parameters likeimpedance, pacing threshold voltage, current drain, longevity, etc. maybe more dependent on the pacing vector, which includes both the cathodeand the anode. The IMD 16 may also provide defibrillation therapy and/orcardioversion therapy via electrodes located on at least one of theleads 18, 20, 22. Further, the IMD 16 may detect arrhythmia of the heart12, such as fibrillation of the ventricles 28, 32, and deliverdefibrillation therapy to the heart 12 in the form of electrical pulses.In some examples, IMD 16 may be programmed to deliver a progression oftherapies, e.g., pulses with increasing energy levels, until afibrillation of heart 12 is stopped.

In some examples, a programmer 24, which may be a handheld computingdevice or a computer workstation, may be used by a user, such as aphysician, technician, another clinician, and/or patient, to communicatewith the IMD 16 (e.g., to program the IMD 16). For example, the user mayinteract with the programmer 24 to retrieve information concerning theeffectiveness of one or more electrodes, one or more detected orindicated faults associated within the IMD 16 and/or the pacing therapydelivered therewith. The IMD 16 and the programmer 24 may be configuredto work together to determine or identify effective electrodes locatedon the leads 18, 20, 22 using the exemplary methods and processesdescribed herein. For instance, computing apparatus located in one orboth of the IMD 16 and the programmer 24 may be configured to analyze orevaluate signals from one or more electrodes to determine theeffectiveness of the electrodes. The IMD 16 and the programmer 24 maycommunicate via wireless communication using any techniques known in theart. Examples of communication techniques may include, e.g., lowfrequency or radiofrequency (RF) telemetry, but other techniques arealso contemplated.

FIG. 2 is a conceptual diagram illustrating the IMD 16 and the leads 18,20, 22 of therapy system 10 of FIG. 1 in more detail. The leads 18, 20,22 may be electrically coupled to a therapy delivery module (e.g., fordelivery of pacing therapy), a sensing module (e.g., for sensing one ormore signals from one or more electrodes configured to contact tissue ofa patient), and/or any other modules of the IMD 16 via a connector block34. In some examples, the proximal ends of the leads 18, 20, 22 mayinclude electrical contacts that electrically couple to respectiveelectrical contacts within the connector block 34 of the IMD 16. Inaddition, in some examples, the leads 18, 20, 22 may be mechanicallycoupled to the connector block 34 with the aid of set screws, connectionpins, or another suitable mechanical coupling mechanism.

Each of the leads 18, 20, 22 includes an elongated insulative lead body,which may carry a number of conductors (e.g., concentric coiledconductors, straight conductors, etc.) separated from one another byinsulation (e.g., tubular insulative sheaths). In the illustratedexample, bipolar electrodes 40, 42 are located proximate to a distal endof the lead 18. In addition, the bipolar electrodes 44, 45, 46, 47 arelocated proximate to a distal end of the lead 20 and the bipolarelectrodes 48, 50 are located proximate to a distal end of the lead 22.

The electrodes 40, 44, 45, 46, 47, 48 may take the form of ringelectrodes, and the electrodes 42, 50 may take the form of extendablehelix tip electrodes mounted retractably within the insulative electrodeheads 52, 54, 56, respectively. Each of the electrodes 40, 42, 44, 45,46, 47, 48, 50 may be electrically coupled to a respective one of theconductors (e.g., coiled and/or straight) within the lead body of itsassociated lead 18, 20, 22, and thereby coupled to respective ones ofthe electrical contacts on the proximal end of the leads 18, 20, 22.

Additionally, electrodes 44, 45, 46 and 47 may have an electrode surfacearea of about 5.3 mm² to about 5.8 mm². Electrodes 44, 45, 46, and 47may also referred to as LV1, LV2, LV3, and LV4, respectively. The LVelectrodes (i.e., left ventricle electrode 1 (LV1) 44, left ventricleelectrode 2 (LV2) 45, left ventricle electrode 3 (LV3) 46, and leftventricle 4 (LV4) 47 etc.) on the lead 20 can be spaced apart atvariable distances. For example, electrode 44 may be a distance of,e.g., about 21 millimeters (mm), away from electrode 45, electrodes 45and 46 may be spaced a distance of, e.g. about 1.3 mm to about 1.5 mm,away from each other, and electrodes 46 and 47 may be spaced a distanceof, e.g. 20 mm to about 21 mm, away from each other.

The electrodes 40, 42, 44, 45, 46, 47, 48, 50 may further be used tosense electrical signals (e.g., morphological waveforms withinelectrograms (EGM)) attendant to the depolarization and repolarizationof the heart 12. The sensed electrical signals may be used to determinewhether the electrodes 40, 42, 44, 45, 46, 47, 48, 50 are effective(e.g., capable of sensing valid cardiac signals, capable of deliveringtherapy, in sufficient contact with cardiac tissue, etc.). Theelectrical signals are conducted to the IMD 16 via the respective leads18, 20, 22. In some examples, the IMD 16 may also deliver pacing pulsesvia the electrodes 40, 42, 44, 45, 46, 47, 48, 50 to causedepolarization of cardiac tissue of the patient's heart 12. In someexamples, as illustrated in FIG. 2A, the IMD 16 includes one or morehousing electrodes, such as housing electrode 58, which may be formedintegrally with an outer surface of a housing 60 (e.g.,hermetically-sealed housing) of the IMD 16 or otherwise coupled to thehousing 60. Any of the electrodes 40, 42, 44, 45, 46, 47, 48 and 50 maybe used for unipolar sensing or pacing in combination with housingelectrode 58. In other words, any of electrodes 40, 42, 44, 45, 46, 47,48, 50, 58 may be used in combination to form a sensing vector, e.g., asensing vector that may be used to evaluate and/or analyze theeffectiveness of pacing therapy. It is generally understood by thoseskilled in the art that other electrodes can also be selected to define,or be used for, pacing and sensing vectors. Further, any of electrodes40, 42, 44, 45, 46, 47, 48, 50, 58, which are not being used to deliverpacing therapy, may be used to sense electrical activity during pacingtherapy.

As described in further detail with reference to FIGS. 3A-3B, thehousing 60 may enclose a therapy delivery module that may include astimulation generator for generating cardiac pacing pulses anddefibrillation or cardioversion shocks, as well as a sensing module formonitoring the patient's heart rhythm. The leads 18, 20, 22 may alsoinclude elongated electrodes 62, 64, 66, respectively, which may takethe form of a coil. The IMD 16 may deliver defibrillation shocks to theheart 12 via any combination of the elongated electrodes 62, 64, 66 andthe housing electrode 58. The electrodes 58, 62, 64, 66 may also be usedto deliver cardioversion pulses to the heart 12. Further, the electrodes62, 64, 66 may be fabricated from any suitable electrically conductivematerial, such as, but not limited to, platinum, platinum alloy, and/orother materials known to be usable in implantable defibrillationelectrodes. Since electrodes 62, 64, 66 are not generally configured todeliver pacing therapy, any of electrodes 62, 64, 66 may be used tosense electrical activity (e.g., for use in determining electrodeeffectiveness, for use in analyzing pacing therapy effectiveness, etc.)and may be used in combination with any of electrodes 40, 42, 44, 45,46, 47, 48, 50, 58. In at least one embodiment, the RV elongatedelectrode 62 may be used to sense electrical activity of a patient'sheart during the delivery of pacing therapy (e.g., in combination withthe housing electrode 58 forming a RV elongated coil, or defibrillationelectrode-to-housing electrode vector).

The configuration of the exemplary therapy system 10 illustrated inFIGS. 1-2 is merely one example. In other examples, the therapy systemmay include epicardial leads and/or patch electrodes instead of or inaddition to the transvenous leads 18, 20, 22 illustrated in FIG. 1.Further, in one or more embodiments, the IMD 16 need not be implantedwithin the patient 14. For example, the IMD 16 may deliver variouscardiac therapies to the heart 12 via percutaneous leads that extendthrough the skin of the patient 14 to a variety of positions within oroutside of the heart 12. In one or more embodiments, the system 10 mayutilize wireless pacing (e.g., using energy transmission to theintracardiac pacing component(s) via ultrasound, inductive coupling, RF,etc.) and sensing cardiac activation using electrodes on the can/housingand/or on subcutaneous leads.

In other examples of therapy systems that provide electrical stimulationtherapy to the heart 12, such therapy systems may include any suitablenumber of leads coupled to the IMD 16, and each of the leads may extendto any location within or proximate to the heart 12. For example, otherexamples of therapy systems may include three transvenous leads locatedas illustrated in FIGS. 1-2. Still further, other therapy systems mayinclude a single lead that extends from the IMD 16 into the right atrium26 or the right ventricle 28, or two leads that extend into a respectiveone of the right atrium 26 and the right ventricle 28.

FIG. 3A is a functional block diagram of one exemplary configuration ofthe IMD 16. As shown, the IMD 16 may include a control module 81, atherapy delivery module 84 (e.g., which may include a stimulationgenerator), a sensing module 86, and a power source 90.

The control module 81 may include a processor 80, memory 82, and atelemetry module 88. The memory 82 may include computer-readableinstructions that, when executed, e.g., by the processor 80, cause theIMD 16 and/or the control module 81 to perform various functionsattributed to the IMD 16 and/or the control module 81 described herein.Further, the memory 82 may include any volatile, non-volatile, magnetic,optical, and/or electrical media, such as a random access memory (RAM),read-only memory (ROM), non-volatile RAM (NVRAM), electrically-erasableprogrammable ROM (EEPROM), flash memory, and/or any other digital media.An exemplary capture management module may be the left ventricularcapture management (LVCM) module described in U.S. Pat. No. 7,684,863issued Mar. 23, 2010, which is incorporated herein by reference in itsentirety.

The processor 80 of the control module 81 may include any one or more ofa microprocessor, a controller, a digital signal processor (DSP), anapplication specific integrated circuit (ASIC), a field-programmablegate array (FPGA), and/or equivalent discrete or integrated logiccircuitry. In some examples, the processor 80 may include multiplecomponents, such as any combination of one or more microprocessors, oneor more controllers, one or more DSPs, one or more ASICs, and/or one ormore FPGAs, as well as other discrete or integrated logic circuitry. Thefunctions attributed to the processor 80 herein may be embodied assoftware, firmware, hardware, or any combination thereof.

The control module 81 may be used to determine the effectiveness of theelectrodes 40, 42, 44, 45, 46, 47, 48, 50, 58, 62, 64, 66 using theexemplary methods and/or processes described herein according to aselected one or more programs, which may be stored in the memory 82.Further, the control module 81 may control the therapy delivery module84 to deliver therapy (e.g., electrical stimulation therapy such aspacing) to the heart 12 according to a selected one or more therapyprograms, which may be stored in the memory 82. More specifically, thecontrol module 81 (e.g., the processor 80) may control variousparameters of the electrical stimulus delivered by the therapy deliverymodule 84 such as, e.g., AV delays, pacing pulses with the amplitudes,pulse widths, frequency, or electrode polarities, etc., which may bespecified by one or more selected therapy programs (e.g., AV delayadjustment programs, pacing therapy programs, pacing recovery programs,capture management programs, etc.). As shown, the therapy deliverymodule 84 is electrically coupled to electrodes 40, 42, 44, 45, 46, 47,48, 50, 58, 62, 64, 66, e.g., via conductors of the respective lead 18,20, 22, or, in the case of housing electrode 58, via an electricalconductor disposed within housing 60 of IMD 16. Therapy delivery module84 may be configured to generate and deliver electrical stimulationtherapy such as pacing therapy to the heart 12 using one or more of theelectrodes 40, 42, 44, 45, 46, 47, 48, 50, 58, 62, 64, 66.

For example, therapy delivery module 84 may deliver pacing stimulus(e.g., pacing pulses) via ring electrodes 40, 44, 45, 46, 47, 48 coupledto leads 18, 20, and 22, respectively, and/or helical tip electrodes 42,50 of leads 18, 20, and 22. Further, for example, therapy deliverymodule 84 may deliver defibrillation shocks to heart 12 via at least twoof electrodes 58, 62, 64, 66. In some examples, therapy delivery module84 may be configured to deliver pacing, cardioversion, or defibrillationstimulation in the form of electrical pulses. In other examples, therapydelivery module 84 may be configured deliver one or more of these typesof stimulation in the form of other signals, such as sine waves, squarewaves, and/or other substantially continuous time signals.

The IMD 16 may further include a switch module 85 and the control module81 (e.g., the processor 80) may use the switch module 85 to select,e.g., via a data/address bus, which of the available electrodes are usedto deliver therapy such as pacing pulses for pacing therapy, or which ofthe available electrodes are used for sensing. The switch module 85 mayinclude a switch array, switch matrix, multiplexer, or any other type ofswitching device suitable to selectively couple the sensing module 86and/or the therapy delivery module 84 to one or more selectedelectrodes. More specifically, the therapy delivery module 84 mayinclude a plurality of pacing output circuits. Each pacing outputcircuit of the plurality of pacing output circuits may be selectivelycoupled, e.g., using the switch module 85, to one or more of theelectrodes 40, 42, 44, 45, 46, 47, 48, 50, 58, 62, 64, 66 (e.g., a pairof electrodes for delivery of therapy to a pacing vector). In otherwords, each electrode can be selectively coupled to one of the pacingoutput circuits of the therapy delivery module using the switchingmodule 85.

The sensing module 86 is coupled (e.g., electrically coupled) to sensingapparatus, which may include, among additional sensing apparatus, theelectrodes 40, 42, 44, 45, 46, 47, 48, 50, 58, 62, 64, 66 to monitorelectrical activity of the heart 12, e.g., electrocardiogram(ECG)/electrogram (EGM) signals, etc. The ECG/EGM signals may be used toidentify the effectiveness of each of the electrodes 40, 42, 44, 46, 48,50, 58, 62, 64, 66 (e.g., by monitoring or measuring the signals foranalysis by the control module 81, the programmer 24, etc.). Further,the ECG/EGM signals may be used to measure or monitor activation times(e.g., ventricular activations times, etc.), heart rate (HR), heart ratevariability (HRV), heart rate turbulence (HRT),deceleration/acceleration capacity, deceleration sequence incidence,T-wave alternans (TWA), P-wave to P-wave intervals (also referred to asthe P-P intervals or A-A intervals), R-wave to R-wave intervals (alsoreferred to as the R-R intervals or V-V intervals), P-wave to QRScomplex intervals (also referred to as the P-R intervals, A-V intervals,or P-Q intervals), QRS-complex morphology, ST segment (i.e., the segmentthat connects the QRS complex and the T-wave), T-wave changes, QTintervals, electrical vectors, etc.

The switch module 85 may be also be used with the sensing module 86 toselect which of the available electrodes are used, or enabled, to, e.g.,sense electrical activity of the patient's heart (e.g., one or moreelectrical vectors of the patient's heart using any combination of theelectrodes 40, 42, 44, 45, 46, 47, 48, 50, 58, 62, 64, 66). Likewise,the switch module 85 may be also be used with the sensing module 86 toselect which of the available electrodes are not to be used (e.g.,disabled) to, e.g., sense electrical activity of the patient's heart(e.g., one or more electrical vectors of the patient's heart using anycombination of the electrodes 40, 42, 44, 45, 46, 47, 48, 50, 58, 62,64, 66). In some examples, the control module 81 may select theelectrodes that function as sensing electrodes via the switch modulewithin the sensing module 86, e.g., by providing signals via adata/address bus.

In some examples, sensing module 86 includes a channel that includes anamplifier with a relatively wider pass band than the R-wave or P-waveamplifiers. Signals from the selected sensing electrodes may be providedto a multiplexer, and thereafter converted to multi-bit digital signalsby an analog-to-digital converter for storage in memory 82, e.g., as anelectrogram (EGM). In some examples, the storage of such EGMs in memory82 may be under the control of a direct memory access circuit. Thecontrol module 81 (e.g., using the processor 80) may employ digitalsignal analysis techniques to characterize the digitized signals storedin memory 82 to analyze and/or classify one or more morphologicalwaveforms of the EGM signals to determine which electrodes are effective(e.g., operable for capturing valid signals), determine which electrodesare ineffective (e.g., inoperable for capturing valid signals),determine pacing therapy effectiveness, etc. For example, the processor80 may be configured to determine, or obtain, one more features of oneor more sensed morphological waveforms within one or more electricalvectors of the patient's heart and store the one or more features withinthe memory 82 for use in comparing features, values, etc. of thewaveforms to determine effectiveness of the electrodes.

In some examples, the control module 81 may operate as an interruptdriven device, and may be responsive to interrupts from pacer timing andcontrol module, where the interrupts may correspond to the occurrencesof sensed P-waves and R-waves and the generation of cardiac pacingpulses. Any necessary mathematical calculations may be performed by theprocessor 80 and any updating of the values or intervals controlled bythe pacer timing and control module may take place following suchinterrupts. A portion of memory 82 may be configured as a plurality ofrecirculating buffers, capable of holding one or more series of measuredintervals, which may be analyzed by, e.g., the processor 80 in responseto the occurrence of a pace or sense interrupt to determine whether thepatient's heart 12 is presently exhibiting atrial or ventriculartachyarrhythmia.

The telemetry module 88 of the control module 81 may include anysuitable hardware, firmware, software, or any combination thereof forcommunicating with another device, such as the programmer 24 asdescribed herein with respect to FIG. 1. For example, under the controlof the processor 80, the telemetry module 88 may receive downlinktelemetry from and send uplink telemetry to the programmer 24 with theaid of an antenna, which may be internal and/or external. The processor80 may provide the data to be uplinked to the programmer 24 and thecontrol signals for the telemetry circuit within the telemetry module88, e.g., via an address/data bus. In some examples, the telemetrymodule 88 may provide received data to the processor 80 via amultiplexer.

The various components of the IMD 16 are further coupled to a powersource 90, which may include a rechargeable or non-rechargeable battery.A non-rechargeable battery may be selected to last for several years,while a rechargeable battery may be inductively charged from an externaldevice, e.g., on a daily or weekly basis.

FIG. 3B is another embodiment of a functional block diagram for IMD 16.FIG. 3B depicts bipolar RA lead 22, bipolar RV lead 18, and bipolar LVCS lead 20 without the LA CS pace/sense electrodes and coupled with animplantable pulse generator (IPG) circuit 31 having programmable modesand parameters of a bi-ventricular DDD/R type known in the pacing art.In turn, the sensor signal processing circuit 91 indirectly couples tothe timing circuit 83 and via data and control bus to microcomputercircuitry 33. The IPG circuit 31 is illustrated in a functional blockdiagram divided generally into a microcomputer circuit 33 and a pacingcircuit 21. The pacing circuit 21 includes the digital controller/timercircuit 83, the output amplifiers circuit 51, the sense amplifierscircuit 55, the RF telemetry transceiver 41, the activity sensor circuit35 as well as a number of other circuits and components described below.

Crystal oscillator circuit 89 provides the basic timing clock for thepacing circuit 21, while battery 29 provides power. Power-on-resetcircuit 87 responds to initial connection of the circuit to the batteryfor defining an initial operating condition and similarly, resets theoperative state of the device in response to detection of a low batterycondition. Reference mode circuit 37 generates stable voltage referenceand currents for the analog circuits within the pacing circuit 21, whileanalog to digital converter ADC and multiplexer circuit 39 digitizesanalog signals and voltage to provide real time telemetry if a cardiacsignals from sense amplifiers 55, for uplink transmission via RFtransmitter and receiver circuit 41. Voltage reference and bias circuit37, ADC and multiplexer 39, power-on-reset circuit 87 and crystaloscillator circuit 89 may correspond to any of those presently used incurrent marketed implantable cardiac pacemakers.

If the IPG is programmed to a rate responsive mode, the signals outputby one or more physiologic sensor are employed as a rate controlparameter (RCP) to derive a physiologic escape interval. For example,the escape interval is adjusted proportionally to the patient's activitylevel developed in the patient activity sensor (PAS) circuit 35 in thedepicted, exemplary IPG circuit 31. The patient activity sensor 27 iscoupled to the IPG housing and may take the form of a piezoelectriccrystal transducer as is well known in the art and its output signal isprocessed and used as the RCP. Sensor 27 generates electrical signals inresponse to sensed physical activity that are processed by activitycircuit 35 and provided to digital controller/timer circuit 83. Activitycircuit 35 and associated sensor 27 may correspond to the circuitrydisclosed in U.S. Pat. No. 5,052,388 issued Oct. 1, 1991 and U.S. Pat.No. 4,428,378 issued Jan. 31, 1984, each of which is incorporated hereinby reference in its entirety. Similarly, the exemplary systems,apparatus, and methods described herein may be practiced in conjunctionwith alternate types of sensors such as oxygenation sensors, pressuresensors, pH sensors and respiration sensors, all well known for use inproviding rate responsive pacing capabilities. Alternately, QT time maybe used as the rate indicating parameter, in which case no extra sensoris required. Similarly, the exemplary embodiments described herein mayalso be practiced in non-rate responsive pacemakers.

Data transmission to and from the external programmer is accomplished byway of the telemetry antenna 57 and an associated RF transceiver 41,which serves both to demodulate received downlink telemetry and totransmit uplink telemetry. Uplink telemetry capabilities will typicallyinclude the ability to transmit stored digital information, e.g.operating modes and parameters, EGM histograms, and other events, aswell as real time EGMs of atrial and/or ventricular electrical activityand marker channel pulses indicating the occurrence of sensed and paceddepolarizations in the atrium and ventricle, as are well known in thepacing art.

Microcomputer 33 contains a microprocessor 80 and associated systemclock and on-processor RAM and ROM chips 82A and 82B, respectively. Inaddition, microcomputer circuit 33 includes a separate RAM/ROM chip 82Cto provide additional memory capacity. Microprocessor 80 normallyoperates in a reduced power consumption mode and is interrupt driven.Microprocessor 80 is awakened in response to defined interrupt events,which may include A-TRIG, RV-TRIG, LV-TRIG signals generated by timersin digital timer/controller circuit 83 and A-EVENT, RV-EVENT, andLV-EVENT signals generated by sense amplifiers circuit 55, among others.The specific values of the intervals and delays timed out by digitalcontroller/timer circuit 83 are controlled by the microcomputer circuit33 by way of data and control bus from programmed-in parameter valuesand operating modes. In addition, if programmed to operate as a rateresponsive pacemaker, a timed interrupt, e.g., every cycle or every twoseconds, may be provided in order to allow the microprocessor to analyzethe activity sensor data and update the basic A-A, V-A, or V-V escapeinterval, as applicable. In addition, the microprocessor 80 may alsoserve to define variable, operative AV delay intervals and the energydelivered to each ventricle.

In one embodiment, microprocessor 80 is a custom microprocessor adaptedto fetch and execute instructions stored in RAM/ROM unit 82 in aconventional manner. It is contemplated, however, that otherimplementations may be suitable to practice the present invention. Forexample, an off-the-shelf, commercially available microprocessor ormicrocontroller, or custom application-specific, hardwired logic, orstate-machine type circuit may perform the functions of microprocessor80.

Digital controller/timer circuit 83 operates under the general controlof the microcomputer 33 to control timing and other functions within thepacing circuit 320 and includes a set of timing and associated logiccircuits of which certain ones pertinent to the present invention aredepicted. The depicted timing circuits include URI/LRI timers 83A, V-Vdelay timer 83B, intrinsic interval timers 83C for timing elapsedV-EVENT to V-EVENT intervals or V-EVENT to A-EVENT intervals or the V-Vconduction interval, escape interval timers 83D for timing A-A, V-A,and/or V-V pacing escape intervals, an AV delay interval timer 83E fortiming the A-LVp delay (or A-RVp delay) from a preceding A-EVENT orA-TRIG, a post-ventricular timer 83F for timing post-ventricular timeperiods, and a date/time clock 83G.

The AV delay interval timer 83E is loaded with an appropriate delayinterval for one ventricular chamber (e.g., either an A-RVp delay or anA-LVp delay as determined using known methods) to time-out starting froma preceding A-PACE or A-EVENT. The interval timer 83E triggers pacingstimulus delivery, and can be based on one or more prior cardiac cycles(or from a data set empirically derived for a given patient).

The post-event timer 83F time out the post-ventricular time periodfollowing an RV-EVENT or LV-EVENT or a RV-TRIG or LV-TRIG andpost-atrial time periods following an A-EVENT or A-TRIG. The durationsof the post-event time periods may also be selected as programmableparameters stored in the microcomputer 33. The post-ventricular timeperiods include the PVARP, a post-atrial ventricular blanking period(PAVBP), a ventricular blanking period (VBP), a post-ventricular atrialblanking period (PVARP) and a ventricular refractory period (VRP)although other periods can be suitably defined depending, at least inpart, on the operative circuitry employed in the pacing engine. Thepost-atrial time periods include an atrial refractory period (ARP)during which an A-EVENT is ignored for the purpose of resetting any AVdelay, and an atrial blanking period (ABP) during which atrial sensingis disabled. It should be noted that the starting of the post-atrialtime periods and the AV delays can be commenced substantiallysimultaneously with the start or end of each A-EVENT or A-TRIG or, inthe latter case, upon the end of the A-PACE which may follow the A-TRIG.Similarly, the starting of the post-ventricular time periods and the V-Aescape interval can be commenced substantially simultaneously with thestart or end of the V-EVENT or V-TRIG or, in the latter case, upon theend of the V-PACE which may follow the V-TRIG. The microprocessor 80also optionally calculates AV delays, post-ventricular time periods, andpost-atrial time periods that vary with the sensor based escape intervalestablished in response to the RCP(s) and/or with the intrinsic atrialrate.

The output amplifiers circuit 51 contains a RA pace pulse generator (anda LA pace pulse generator if LA pacing is provided), a RV pace pulsegenerator, and a LV pace pulse generator or corresponding to any ofthose presently employed in commercially marketed cardiac pacemakersproviding atrial and ventricular pacing. In order to trigger generationof an RV-PACE or LV-PACE pulse, digital controller/timer circuit 83generates the RV-TRIG signal at the time-out of the A-RVp delay (in thecase of RV pre-excitation) or the LV-TRIG at the time-out of the A-LVpdelay (in the case of LV pre-excitation) provided by AV delay intervaltimer 83E (or the V-V delay timer 83B). Similarly, digitalcontroller/timer circuit 83 generates an RA-TRIG signal that triggersoutput of an RA-PACE pulse (or an LA-TRIG signal that triggers output ofan LA-PACE pulse, if provided) at the end of the V-A escape intervaltimed by escape interval timers 83D.

The output amplifiers circuit 51 includes switching circuits forcoupling selected pace electrode pairs from among the lead conductorsand the IND_CAN electrode 20 to the RA pace pulse generator (and LA pacepulse generator if provided), RV pace pulse generator and LV pace pulsegenerator. Pace/sense electrode pair selection and control circuit 53selects lead conductors and associated pace electrode pairs to becoupled with the atrial and ventricular output amplifiers within outputamplifiers circuit 51 for accomplishing RA, LA, RV and LV pacing.

The sense amplifiers circuit 55 contains sense amplifiers correspondingto any of those presently employed in contemporary cardiac pacemakersfor atrial and ventricular pacing and sensing. High impedance P-wave andR-wave sense amplifiers may be used to amplify a voltage differencesignal that is generated across the sense electrode pairs by the passageof cardiac depolarization wavefronts. The high impedance senseamplifiers use high gain to amplify the low amplitude signals and relyon pass band filters, time domain filtering and amplitude thresholdcomparison to discriminate a P-wave or R-wave from background electricalnoise. Digital controller/timer circuit 83 controls sensitivity settingsof the atrial and ventricular sense amplifiers 55.

The sense amplifiers are typically uncoupled from the sense electrodesduring the blanking periods before, during, and after delivery of a pacepulse to any of the pace electrodes of the pacing system to avoidsaturation of the sense amplifiers. The sense amplifiers circuit 55includes blanking circuits for uncoupling the selected pairs of the leadconductors and the IND-CAN electrode 20 from the inputs of the RA senseamplifier (and LA sense amplifier if provided), RV sense amplifier andLV sense amplifier during the ABP, PVABP and VBP. The sense amplifierscircuit 55 also includes switching circuits for coupling selected senseelectrode lead conductors and the IND-CAN electrode 20 to the RA senseamplifier (and LA sense amplifier if provided), RV sense amplifier andLV sense amplifier. Again, sense electrode selection and control circuit53 selects conductors and associated sense electrode pairs to be coupledwith the atrial and ventricular sense amplifiers within the outputamplifiers circuit 51 and sense amplifiers circuit 55 for accomplishingRA, LA, RV and LV sensing along desired unipolar and bipolar sensingvectors.

Right atrial depolarizations or P-waves in the RA-SENSE signal that aresensed by the RA sense amplifier result in a RA-EVENT signal that iscommunicated to the digital controller/timer circuit 83. Similarly, leftatrial depolarizations or P-waves in the LA-SENSE signal that are sensedby the LA sense amplifier, if provided, result in a LA-EVENT signal thatis communicated to the digital controller/timer circuit 83. Ventriculardepolarizations or R-waves in the RV-SENSE signal are sensed by aventricular sense amplifier result in an RV-EVENT signal that iscommunicated to the digital controller/timer circuit 83. Similarly,ventricular depolarizations or R-waves in the LV-SENSE signal are sensedby a ventricular sense amplifier result in an LV-EVENT signal that iscommunicated to the digital controller/timer circuit 83. The RV-EVENT,LV-EVENT, and RA-EVENT, LA-SENSE signals may be refractory ornon-refractory, and can inadvertently be triggered by electrical noisesignals or aberrantly conducted depolarization waves rather than trueR-waves or P-waves.

As described herein, various exemplary systems, methods, and interfacesmay be configured to use electrode apparatus including externalelectrodes, imaging apparatus, display apparatus, and computingapparatus to noninvasively assist a user (e.g., a physician) inselecting one or more locations (e.g., implantation site regions)proximate a patient's heart for one or more implantable electrodesand/or to navigate one or more implantable electrodes to the selectedlocation(s). An exemplary system 100 including electrode apparatus 110,imaging apparatus 120, display apparatus 130, and computing apparatus140 is depicted in FIG. 4.

The electrode apparatus 110 as shown includes a plurality of electrodesincorporated, or included within a band wrapped around the chest, ortorso, of a patient 14. The electrode apparatus 110 is operativelycoupled to the computing apparatus 140 (e.g., through one or more wiredelectrical connections, wirelessly, etc.) to provide electrical signalsfrom each of the electrodes to the computing apparatus 140 for analysis.Exemplary electrode apparatus may be described in U.S. ProvisionalPatent Application 61/913,759 entitled “Bioelectric Sensor Device andMethods” and filed on Dec. 9, 2013 and U.S. patent application Ser. No.14/227,719 entitled “Bioelectric Sensor Device and Methods” and filed onMar. 27, 2014 and issued as U.S. Pat. No. 9,320,446 on Apr. 26, 2016,each of which is incorporated herein by reference in its entirety.Further, exemplary electrode apparatus 110 will be described in moredetail in reference to FIGS. 5A-5B.

The imaging apparatus 120 may be any type of imaging apparatusconfigured to image, or provide images of, at least a portion of thepatient in a non-invasive manner. For example, the imaging apparatus 120may not use any components or parts that may be located within thepatient to provide images of at least a portion of the patient exceptnon-invasive tools such as contrast solution. It is to be understoodthat the exemplary systems, methods, and interfaces described herein maynoninvasively assist a user (e.g., a physician) in selecting a locationproximate a patient's heart for an implantable electrode, and after theexemplary systems, methods, and interfaces have provided noninvasiveassistance, the exemplary systems, methods, and interfaces may thenprovide assistance to implant, or navigate, an implantable electrodeinto the patient, e.g., proximate the patient's heart.

For example, after the exemplary systems, methods, and interfaces haveprovided noninvasive assistance, the exemplary systems, methods, andinterfaces may then provide image guided navigation that may be used tonavigate leads including electrodes, leadless electrodes, wirelesselectrodes, catheters, etc., within the patient's body. Further,although the exemplary systems, methods, and interfaces are describedherein with reference to a patient's heart, it is to be understood thatthe exemplary systems, methods, and interfaces may be applicable to anyother portion of the patient's body.

The imaging apparatus 120 may be configured to capture, or take, x-rayimages (e.g., two dimensional x-ray images, three dimensional x-rayimages, etc.) of the patient 14. The imaging apparatus 120 may beoperatively coupled (e.g., through one or more wired electricalconnections, wirelessly, etc.) to the computing apparatus 140 such thatthe images captured by the imaging apparatus 120 may be transmitted tothe computing apparatus 140. Further, the computing apparatus 140 may beconfigured to control the imaging apparatus 120 to, e.g., configure theimaging apparatus 120 to capture images, change one or more settings ofthe imaging apparatus 120, etc.

It will be recognized that while the imaging apparatus 120 as shown inFIG. 4 may be configured to capture x-ray images, any other alternativeimaging modality may also be used by the exemplary systems, methods, andinterfaces described herein. For example, the imaging apparatus 120 maybe configured to capture images, or image data, using isocentricfluoroscopy, bi-plane fluoroscopy, ultrasound, computed tomography (CT),multi-slice computed tomography (MSCT), magnetic resonance imaging(MRI), high frequency ultrasound (HIFU), optical coherence tomography(OCT), intra-vascular ultrasound (IVUS), two dimensional (2D)ultrasound, three dimensional (3D) ultrasound, four dimensional (4D)ultrasound, intraoperative CT, intraoperative MRI, etc. Further, it isto be understood that the imaging apparatus 120 may be configured tocapture a plurality of consecutive images (e.g., continuously) toprovide video frame data. In other words, a plurality of images takenover time using the imaging apparatus 120 may provide motion picturedata. Additionally, the images may also be obtained and displayed intwo, three, or four dimensions. In more advanced forms, four-dimensionalsurface rendering of the heart or other regions of the body may also beachieved by incorporating heart data or other soft tissue data from anatlas map or from pre-operative image data captured by MRI, CT, orechocardiography modalities. Image datasets from hybrid modalities, suchas positron emission tomography (PET) combined with CT, or single photonemission computer tomography (SPECT) combined with CT, could alsoprovide functional image data superimposed onto anatomical data to beused to confidently reach target locations within the heart or otherareas of interest.

The display apparatus 130 and the computing apparatus 140 may beconfigured to display and analyze data such as, e.g., surrogateelectrical activation data, image data, mechanical motion data, etc.gathered, or collected, using the electrode apparatus 110 and theimaging apparatus 120 to noninvasively assist a user in locationselection of an implantable electrode. In at least one embodiment, thecomputing apparatus 140 may be a server, a personal computer, or atablet computer. The computing apparatus 140 may be configured toreceive input from input apparatus 142 and transmit output to thedisplay apparatus 130. Further, the computing apparatus 140 may includedata storage that may allow for access to processing programs orroutines and/or one or more other types of data, e.g., for driving agraphical user interface configured to noninvasively assist a user inlocation selection of an implantable electrode, etc.

The computing apparatus 140 may be operatively coupled to the inputapparatus 142 and the display apparatus 130 to, e.g., transmit data toand from each of the input apparatus 142 and the display apparatus 130.For example, the computing apparatus 140 may be electrically coupled toeach of the input apparatus 142 and the display apparatus 130 using,e.g., analog electrical connections, digital electrical connections,wireless connections, bus-based connections, network-based connections,internet-based connections, etc. As described further herein, a user mayprovide input to the input apparatus 142 to manipulate, or modify, oneor more graphical depictions displayed on the display apparatus 130 toview and/or select one or more target or candidate locations of aportion of a patient's heart as further described herein.

Although as depicted the input apparatus 142 is a keyboard, it is to beunderstood that the input apparatus 142 may include any apparatuscapable of providing input to the computing apparatus 140 to perform thefunctionality, methods, and/or logic described herein. For example, theinput apparatus 142 may include a mouse, a trackball, a touchscreen(e.g., capacitive touchscreen, a resistive touchscreen, a multi-touchtouchscreen, etc.), etc. Likewise, the display apparatus 130 may includeany apparatus capable of displaying information to a user, such as agraphical user interface 132 including graphical depictions of anatomyof a patient's heart, images of a patient's heart, graphical depictionsof locations of one or more electrodes, graphical depictions of one ormore target or candidate locations, alphanumeric representations of oneor more values, graphical depictions or actual images of implantedelectrodes and/or leads, etc. For example, the display apparatus 130 mayinclude a liquid crystal display, an organic light-emitting diodescreen, a touchscreen, a cathode ray tube display, etc.

The graphical user interfaces 132 displayed by the display apparatus 130may include, or display, one or more regions used to display graphicaldepictions, to display images, to allow selection of one or more regionsor areas of such graphical depictions and images, etc. As used herein, a“region” of a graphical user interface 132 may be defined as a portionof the graphical user interface 132 within which information may bedisplayed or functionality may be performed. Regions may exist withinother regions, which may be displayed separately or simultaneously. Forexample, smaller regions may be located within larger regions, regionsmay be located side-by-side, etc. Additionally, as used herein, an“area” of a graphical user interface 132 may be defined as a portion ofthe graphical user interface 132 located with a region that is smallerthan the region it is located within. Exemplary systems and interfacesmay be described in U.S. Provisional Patent Application 61/913,743entitled “Noninvasive Cardiac Therapy Evaluation” and filed on Dec. 9,2013 and U.S. patent application Ser. No. 14/228,009 entitled“Noninvasive Cardiac Therapy Evaluation” and filed on Mar. 27, 2014,each of which is incorporated herein by reference in its entirety.

The processing programs or routines stored and/or executed by thecomputing apparatus 140 may include programs or routines forcomputational mathematics, matrix mathematics, decomposition algorithms,compression algorithms (e.g., data compression algorithms), calibrationalgorithms, image construction algorithms, signal processing algorithms(e.g., Fourier transforms, fast Fourier transforms, etc.),standardization algorithms, comparison algorithms, vector mathematics,or any other processing required to implement one or more exemplarymethods and/or processes described herein. Data stored and/or used bythe computing apparatus 140 may include, for example, image data fromthe imaging apparatus 120, electrical signal data from the electrodeapparatus 110, graphics (e.g., graphical elements, icons, buttons,windows, dialogs, pull-down menus, graphic areas, graphic regions, 3Dgraphics, etc.), graphical user interfaces, results from one or moreprocessing programs or routines employed according to the disclosureherein, or any other data that may be necessary for carrying out the oneand/or more processes or methods described herein.

In one or more embodiments, the exemplary systems, methods, andinterfaces may be implemented using one or more computer programsexecuted on programmable computers, such as computers that include, forexample, processing capabilities, data storage (e.g., volatile ornon-volatile memory and/or storage elements), input devices, and outputdevices. Program code and/or logic described herein may be applied toinput data to perform functionality described herein and generatedesired output information. The output information may be applied asinput to one or more other devices and/or methods as described herein oras would be applied in a known fashion.

The one or more programs used to implement the systems, methods, and/orinterfaces described herein may be provided using any programmablelanguage, e.g., a high level procedural and/or object orientatedprogramming language that is suitable for communicating with a computersystem. Any such programs may, for example, be stored on any suitabledevice, e.g., a storage media, that is readable by a general or specialpurpose program running on a computer system (e.g., including processingapparatus) for configuring and operating the computer system when thesuitable device is read for performing the procedures described herein.In other words, at least in one embodiment, the exemplary systems,methods, and/or interfaces may be implemented using a computer readablestorage medium, configured with a computer program, where the storagemedium so configured causes the computer to operate in a specific andpredefined manner to perform functions described herein. Further, in atleast one embodiment, the exemplary systems, methods, and/or interfacesmay be described as being implemented by logic (e.g., object code)encoded in one or more non-transitory media that includes code forexecution and, when executed by a processor, is operable to performoperations such as the methods, processes, and/or functionalitydescribed herein.

The computing apparatus 140 may be, for example, any fixed or mobilecomputer system (e.g., a controller, a microcontroller, a personalcomputer, mini computer, tablet computer, etc.). The exact configurationof the computing apparatus 130 is not limiting, and essentially anydevice capable of providing suitable computing capabilities and controlcapabilities (e.g., graphics processing, etc.) may be used. As describedherein, a digital file may be any medium (e.g., volatile or non-volatilememory, a CD-ROM, a punch card, magnetic recordable tape, etc.)containing digital bits (e.g., encoded in binary, trinary, etc.) thatmay be readable and/or writeable by computing apparatus 140 describedherein. Also, as described herein, a file in user-readable format may beany representation of data (e.g., ASCII text, binary numbers,hexadecimal numbers, decimal numbers, graphically, etc.) presentable onany medium (e.g., paper, a display, etc.) readable and/or understandableby a user.

In view of the above, it will be readily apparent that the functionalityas described in one or more embodiments according to the presentdisclosure may be implemented in any manner as would be known to oneskilled in the art. As such, the computer language, the computer system,or any other software/hardware which is to be used to implement theprocesses described herein shall not be limiting on the scope of thesystems, processes or programs (e.g., the functionality provided by suchsystems, processes or programs) described herein.

FIGS. 5A-5B are conceptual diagrams illustrating exemplary electrodesystems and apparatus for measuring body-surface potentials and, moreparticularly, torso-surface potentials. As shown in FIG. 5A, theexemplary electrode system 110 includes a set or array of electrodes102, a strap 104, interface/amplifier circuitry 103, and computingapparatus 140 such as described herein with reference to FIG. 4. Theelectrodes 102 are attached, or coupled, to the strap 104 that isconfigured to be wrapped around the torso of patient such that theelectrodes 102 surround the patient's heart. As further illustrated, theelectrodes 102 may be positioned around the circumference of patient,including the posterior, lateral, and anterior surfaces of the torso ofpatient. In other examples, electrodes 102 may be positioned on any oneor more of the posterior, lateral, and anterior surfaces of the torso.Further, the electrodes 102 may be electrically connected tointerface/amplifier circuitry 103 via wired connection 108. Theinterface/amplifier circuitry 103 may be configured to amplify thesignals from the electrodes 102 and provide the signals to the computingapparatus 140. Other exemplary systems may use a wireless connection totransmit the signals sensed by electrodes 102 to the interface/amplifiercircuitry 103 and, in turn, the computing apparatus 140, e.g., aschannels of data.

Although in the example of FIG. 5A, the system 110 includes a strap 104,in other examples any of a variety of mechanisms, e.g., tape oradhesives, may be employed to aid in the spacing and placement ofelectrodes 102. In other examples, the electrodes 102 may be placedindividually on the torso of a patient. Further, in other examples,electrodes 102 (e.g., arranged in an array) may be part of, or locatedwithin, patches, vests, and/or other means of securing the electrodes102 to the torso of the patient.

The electrodes 102 may be configured to surround the heart of thepatient and record, or monitor, the electrical signals associated withthe depolarization repolarization of the heart after the signals havepropagated through the torso of patient. Each of the electrodes 102 maybe used in a unipolar configuration to sense the torso-surfacepotentials that reflect the cardiac signals. The interface/amplifiercircuitry 103 may also be coupled to a return or indifferent electrode(not shown) which may be used in combination with each of electrodes 102for unipolar sensing. In some examples, there may be about 12 to about50 electrodes 102 spatially distributed around the torso of patient.Other configurations may have more or fewer electrodes 102.

The computing apparatus 140 may record and analyze the torso-surfacepotential signals sensed by electrodes 102 and amplified/conditioned bythe interface/amplifier circuitry 103. For example, the sensing andcomputing apparatus described in U.S. Pat. App. Pub. No. 2012/0283587 A1published Nov. 8, 2012 and U.S. Pat. App. Pub. No. 2012/0284003 A1published Nov. 8, 2012, each of which is incorporated herein byreference in its entirety, may be used to record and analyzetorso-surface potential signals. The computing apparatus 140 may beconfigured to analyze the signals from the electrodes 102 to determinewhether each electrode of the electrodes 102 is effective (e.g.,operable for monitoring or sensing signals from the tissue, or skin, ofthe patient).

FIG. 5B illustrates another exemplary electrode system 111 that includesa plurality of electrodes 112 configured to surround the heart of thepatient and record, or monitor, the electrical signals associated withthe depolarization and repolarization of the heart after the signalshave propagated through the torso of patient. The electrode system 111may include a vest 114 upon which the plurality of electrodes isattached, or to which they are coupled. In at least one embodiment, theplurality, or array, of electrodes 112 may be used to evaluateelectrical dyssynchrony in the heart of the patient. Similar to thesystem 110, the system 111 may include interface/amplifier circuitry 113electrically coupled to each of the electrodes 112 through a wiredconnection 118 and configured to transmit signals from the electrodes112 to a computing apparatus 140. As illustrated, the electrodes 112 maybe distributed over the torso of patient, including, for example, theanterior, lateral, and posterior surfaces of the torso of patient.

The vest 114 may be formed of fabric, or any other material, with theelectrodes 112 attached to thereto. The vest 114 may be configured tomaintain the position and spacing of electrodes 112 on the torso of thepatient. Further, the vest 114 may be marked to assist in determiningthe location of the electrodes 112 on the surface of the torso of thepatient. The vest 114 may also be one piece or in multiple pieces toallow simple placement on the anterior and posterior of the patientusing anatomical landmarks such as the spine and sternum of the patient.Further, the vest 114 may also be, or be used in conjunction with, abelt or patch(es) including electrodes 112. In some examples, there maybe about 25 to about 256 electrodes 112 distributed around the torso ofthe patient, though other configurations may have more or fewerelectrodes 112.

The exemplary systems, apparatus, and/or methods described herein areconfigured to identify effective electrodes, and the systems includingelectrodes, computing apparatus, and display apparatus described hereinwith reference to FIGS. 1-5 may utilize the exemplary systems,apparatus, and/or methods. More specifically, the exemplary systems,apparatus, and/or methods may be used to determine which electrodes inthe systems of FIGS. 1-5 may be effective (or ineffective) for sensingsignals from tissue of the patient and/or pacing tissue of the patient.After it is determined which electrodes are effective, the electrodesmay be used to assist a user (e.g., a physician) in determiningeffective pacing vectors, navigating or locating one or more electrodes(e.g., implantable electrodes, electrodes on leads, leadless/wirelesselectrodes, etc.) to one or more regions of a patient's heart fortherapy, to monitor and display information with respect to the cardiachealth of the patient (e.g., before, during, and after implantation ofcardiac therapy device), etc.

When the band 104 of the surface electrode array system 110 of FIG. 5Aor the vest 114 of the surface electrode array system 111 of FIG. 5B islocated, or placed, on a patient, some of the electrodes 102, 112 maynot be in sufficient contact (e.g., not proper contact, not full orcomplete contact, partial contact, etc.) with the skin of the patient,and thus, may not provide a valid signal (e.g., cardiac signal) from thepatient. As such, the exemplary systems, apparatus, and/or methods maybe used with the systems 110, 111 of FIGS. 5A-5B to determine whichelectrodes 102, 112 are effective for sensing valid electrical activity(e.g., not noise) from the skin of the patient.

Further, for example, when the leads 18, 20, 22 of the system 10 ofFIGS. 1-3 are located, or implanted, in a patient's heart, some of theelectrodes 40, 42, 44, 45, 46, 47, 48, 50, 58, 62, 64, 66 may not be insufficient contact (e.g., not proper contact, not full or completecontact, partial contact, etc.) with the cardiac tissue of the patient,which may not provide sufficient sensing of cardiac signals and/orpacing functionality. As such, the exemplary systems, apparatus, and/ormethods may be used with the system 10 of FIGS. 1-3 to determine whichelectrodes 40, 42, 44, 45, 46, 47, 48, 50, 58, 62, 64, 66 are effectivefor sensing valid electrical activity (e.g., not noise) from the cardiactissue of the patient and/or delivering effective electrical therapy tothe cardiac tissue of the patient.

An exemplary method 144 for identifying effective electrodes in aplurality of electrodes is depicted in FIG. 6. The exemplary method 144may be described as using single signal analysis because, for eachelectrode, only the signal from that electrode is used to determinewhether the electrode is effective. Although the exemplary method 144 isdescribed herein with respect to determining the effectiveness of asingle electrode, it is to be understood that the method 144 could berepeated (e.g., performed sequentially one electrode at a time) orperformed simultaneously for a plurality of electrodes such that eachelectrode of a plurality of electrodes may be evaluated and determinedto be either effective or ineffective.

Before executing method 144, an electrode may be located proximatetissue of a patient configured to sense a signal from the patient. Forexample, an electrode 102 of the system 110 may be located proximate thetorso of a patient and configured to monitor a signal from the skin ofthe torso of the patient. To determine whether the electrode iseffective, the exemplary method 144 may monitor a signal from theelectrode 145.

The exemplary method 144 may then store a portion of the signal from theelectrode for each cardiac cycle of at least two cardiac cycles 146. Forexample, a portion from a first cardiac cycle may be stored and aportion from a second cardiac cycle (e.g., subsequent the first cardiaccycle) may be stored. A portion of the signal may be described as beinga “window” or “snapshot” of the signal taken over a preset time period.For example, the preset time period of the portion of the signal may bebetween about 80 milliseconds (ms) to about 400 ms, such as, e.g., about80 ms, about 100 ms, about 150 ms, about 200 ms, about 250 ms, about 300ms, about 350 ms, about 400 ms, etc. The time period may be described asbeing “preset” because, e.g., the time period may be set by a user.

Each portion of the signal may correspond to the same time frame withineach cardiac cycle. In other words, each portion may occur during thesame part or region of the cardiac cycle. To identify or select theportion of the signal that corresponds to the same time frame withineach cardiac cycle, the exemplary method 144 may use one or morerecurring fiducial elements, markers, or values within the signal or anyother cardiac parameter. In other words, to store a portion of thesignal for each cardiac cycle 146, the exemplary method 144 may store aportion of the signal based on a recurring fiducial element within acardiac signal or parameter.

The recurring fiducial element may include one or more of a ventricularevent (e.g., a ventricular pace, a ventricular sense, etc.), an atrialevent (e.g., an atrial pace, an atrial sense, etc.), a maximum value(e.g., a peak of a QRS complex, a peak of a P-wave, etc.), a minimumvalue, a maximum slope value (e.g., a maximum slope of an R-wave, etc.),an amplitude or slope of atrial or ventricular depolarization signal, acrossing of a predefined threshold, etc. The timing of recurringfiducial element, or time when the recurring fiducial occurs, may beused to base the portion of the signal upon. For example, the start offiducial element may start the time frame or window to store a portionof the signal.

For example, the exemplary method 144 may store a 250 ms portion of thesignal starting from a ventricular pace (i.e., the selected fiducialelement). As such, a first portion may be recorded, or stored, from thestart of a ventricular pace for 250 ms during a first a cardiac cycle,and a second portion may be recorded, or stored, from the start of aventricular pace for 250 ms during a second cardiac cycle that issubsequent to the first cardiac cycle.

After at least two portions have been stored 146, the exemplary method144 may compare the at least two stored portions of the signal toprovide an effectiveness value 147 or other effectiveness informationrepresentative of such comparison. The effectiveness value may berepresentative of the effectiveness of the electrode for using insensing signals from the tissue of the patient and/or deliveringelectrical therapy to the tissue of the patient.

The effectiveness value may be a correlation value or coefficient (e.g.,a Pearson correlation coefficient). Although not shown, the exemplarymethod 144 may then enable (e.g., use) the electrode if is determined tobe effective and/or may disable (e.g., not use or utilize) the electrodeif is determined to be ineffective. To determine whether an electrode iseffective based on an effectiveness value, the effectiveness value maybe compared to a threshold value. If the electrode has an effectivenessvalue greater than or equal to the threshold value, then the electrodemay be enabled. If the electrode has an effectiveness value below thethreshold value, then the electrode may be disabled.

In an embodiment where the effectiveness value is a Pearson correlationcoefficient, the threshold value may be between about 0.5 and 0.98 suchas, e.g., 0.8. For example, the threshold value may be greater than orequal to about 0.5, greater than or equal to about 0.6, greater than orequal to about 0.7, greater than or equal to about 0.75, greater than orequal to about 0.8, etc. and/or may be less than or equal to about 0.8,less than or equal to about 0.85, less than or equal to about 0.9, lessthan or equal to about 0.95, less than or equal to about 0.98, etc.

In an embodiment where the effectiveness value is a waveform matchpercentage, the threshold value may be between about 50% and 100% suchas, e.g., 70%. Waveform match percentages may be generated and/orcalculated using various techniques and/or process, e.g., as describedin U.S. Pat. No. 6,393,316 B1 entitled “METHOD AND APPARATUS FORDETECTION AND TREATMENT OF CARDIAC ARRHYTHMIAS” issued May 21, 2002,which is incorporated herein by reference in its entirety. For example,the threshold value may be greater than or equal to about 50%, greaterthan or equal to about 60%, greater than or equal to about 70%, greaterthan or equal to about 75%, greater than or equal to about 80%, etc.and/or may be less than or equal to about 100%, less than or equal toabout 95%, less than or equal to about 90%, less than or equal to about85%, less than or equal to about 88%, etc.

Prior to the comparison, the portions of the cardiac signal may bealigned to compensate for noise-related jitter of the fiducial elementwith each portion. For example, the portions may be aligned based ontiming of at least one of the following features of the signal, orfiducial element: maximum slope, minimum slope, maximum value, minimumvalue within each window etc. In at least one embodiment, alignment maybe performed based on timing of the maximum value, the minimum value,and/or the greater of the magnitudes of the maximum value and theminimum value.

In at least one embodiment, an exemplary graphical user interface maygraphically depict a plurality of electrodes correlating to a pluralityof actual, physical electrodes in a contact with the patient. Thegraphical user interface may identify which electrodes are determined tobe effective and which electrodes are determined to be ineffective. Auser may use the graphical user interface to enable or disable each ofthe electrodes. In other words, a user may be allowed to turn “off” orturn “on” each electrode via a user interface/program that controls theamplifiers and A/D converters.

Further, a vest or belt of electrodes may not fit correctly (e.g., toolarge, too small, etc.) about a patient such that one or more of theelectrodes may not make contact with the patient so as to provide aneffective electrical signal. A user (e.g., a physician) may recognizewhich electrodes may not be effective and use a graphical user interfaceto disable the electrodes recognized to be ineffective.

Another exemplary method 156 for identifying effective electrodes of aplurality of electrodes is depicted in FIG. 7. The method 156 mayinclude selecting a recurring timing fiducial element 149 to base thewindowing (e.g., framing, cropping, etc.) portions of the signal foreach cardiac cycle. As described herein, the recurring timing fiducialelement may be one or more morphological features of a cardiac signalsuch as, e.g., a maximum value of the signal, etc. The method 156 maythen window a portion of the signal of at least two heart beats, orcardiac cycles 150. For example, if the fiducial element is a maximumvalue and the preset time period is 200 ms, the exemplary method 156 maywindow 200 ms portions of the signal about the maximum value for eachcardiac cycle 150. The window may be selected such that the recurringtime fiducial element is centered within the window (time frame), startsthe window, ends the window, etc. In other words, the recurring timingfiducial element may start the capture window, stop the capture window,or be located halfway through the capture window.

After at least two windowed signals have been stored or captured 150, acorrelation may be computed between the two windowed portions 151resulting in an effectiveness value. As described herein, in at leastone embodiment, a Pearson correlation coefficient may be calculated asthe effectiveness value, or in another embodiment, a waveform matchpercentage may be calculated as the effectiveness value. Based on theeffectiveness value, the method 156 may identify if the electrode iseffective 152, e.g., using a threshold value, etc.

The method 156 may determine the effectiveness of more than oneelectrode simultaneously since the signal of each electrode is comparedto itself and is not determined based on other signals. In other words,the method 156 may be described as being configured to identify aneffective electrode using single signal correlation. For example, if anexemplary system includes eight electrodes, the signal of each of theeight electrodes may be windowed about a fiducial element for at leasttwo cardiac cycles 150 and a correlation may be computed between the atleast two windowed signals 151 for each electrode resulting in aneffectiveness value for each electrode. The effectiveness value may beused to identify which of the 8 electrodes are effective.

Exemplary systems may require a selected number or percentage ofeffective electrodes, e.g., of those electrodes available in the array.For example, the method 156 may further include a check to confirm thata selected number of electrodes are effective 153. If such a selectednumber of electrodes out of the provided electrodes are determined to beeffective 153, then the method 156 may proceed to enabling the effectiveelectrodes 154 and indicating that the system has been initialized, isready for sensing procedures, etc. To determine if enough electrodes outof the provided electrodes are effective, the method 156 may compare thenumber of effective electrodes to a threshold value. For example, in asystem that includes 50 electrodes, the threshold may be 40 electrodes.Thus, if the 40 or more electrodes are determined to be effective, thenthe method 156 may proceed to enabling the 40 effective electrodes anddisabling the 10 ineffective electrodes.

If it is determined that not enough electrodes are effective 153, themethod 156 may optionally re-adjust the electrode positioning 155. Forexample, a system or device may suggest to a user to re-adjust theelectrode positioning. In the case of a vest including a plurality ofelectrodes, a user may adjust the vest such that more electrodes makebetter contact with the skin of the user. Further, the method 156 mayrestart the identification procedure for each of the electrodes if it isdetermined that not enough electrodes are effective 153 (as signified bythe return arrow to windowing the signal of each beat about a fiducialelement 150).

Signals, such as, e.g., cardiac signals, collected, or monitored from anelectrode in a spatial sensor-array may be correlative (e.g., highlycorrelative) with signals monitored by neighbor electrodes in thespatial sensor-array (e.g., electrodes located in relatively closeproximity to one another) if the signals are physiological. Likewise, alack of, or low, correlation between signals monitored may indicate“bad” or non-physiologic signals. In other words, low correlation mayindicate the one or more electrodes are ineffective (e.g., ineffectivefor sensing, ineffective for delivering therapy, etc.). One or moreexemplary automated methods, or algorithms, are described herein thatmay use correlation coefficients between signals collected by multipleelectrodes to determine “bad” or ineffective electrodes (or to determine“good” or effective electrodes).

For example, an exemplary array of electrodes 160 is depicted in FIG. 8.In at least one embodiment, the array of electrodes 160 may beconfigured to be located adjacent the torso of a patient. As shown, thearray 160 includes a plurality of rows 162 of electrodes. Each row 162may be described as being spaced apart from another. In other words,each row 162 is spatially oriented which respect to each other. Further,each electrode within each row 162 is spaced apart from one another. Inat least one embodiment, the spacing between rows and/or electrodeswithin each row may be uniform. In at least one embodiment, the spacebetween electrodes may be about 0.5 centimeters (cm) to about 5 cm, suchas, e.g., 1 cm, 2 cm, 3 cm, etc. In at least one embodiment, the spacebetween electrodes may be as small as 1 millimeter (mm) (e.g., forintracardiac mapping). In at least one embodiment, the space betweenelectrodes may be about 0.1 mm to about 5 mm, such as, e.g., 0.2 mm, 0.5mm, 1 mm, 1.5 mm, 2.0 mm, 3.0 mm, etc.

Further, for purposes of description of the exemplary methods and/orprocesses, the electrodes may be described in terms of primaryelectrodes and proximate neighbor electrodes. The primary electrode isthe electrode that is being evaluated for effectiveness using theexemplary methods and/or processes while the proximate neighborelectrodes are the one or more electrodes that may be used to evaluatethe effectiveness of the primary electrode.

As shown in the array 160, primary electrode 164 has two proximateneighbor electrodes 166. Although in this example, the primary electrode164 has two proximate neighbor electrodes 166, in other embodiments, theprimary electrode may have only one proximate neighbor electrode or morethan two proximate neighbor electrodes. Although the neighbor electrodes166 are located in the same row as the primary electrode 164 asdepicted, in other embodiments, neighbor electrodes 166 may be locatedin rows adjacent to the row containing the primary electrode 164.

In at least one embodiment, the correlation of a depolarization signalat each electrode may be evaluated with two adjacent neighbor electrodes(e.g., vertical neighbors or electrodes along the same line). Forexample, a correlation may be computed, or generated, between thedepolarization signal monitored by a primary electrode and thedepolarization signal monitored at each of two adjacent neighborelectrodes resulting in two correlation values (e.g., each correlationvalue corresponding to a pair of electrodes that includes the primaryelectrode). The greater of the two correlation values may be assigned tothe primary electrode and used to determine whether the primaryelectrode is effective or ineffective. The method or algorithm may berepresented as follows: Greater (corrcoef(signal(j), signal(j+1)),corrcoef (signal(j), signal(j−1)). Primary electrodes located at anextremity, or end, of a vertical line of electrodes will only have onevertical neighbor electrode, and thus, a single correlation value may begenerated, or computed, for that primary electrode.

An exemplary method of identifying an effective electrode using spatialsignal correlation, e.g., using the electrode array of FIG. 8, isdepicted in FIG. 9. The method 170 includes monitoring a first signalfrom a patient using a primary electrode 172 and monitoring one or moresecondary signals from the patient using one or more neighbor electrodes174. The neighbor electrode may be located spatially adjacent theprimary electrode (e.g., within 3 cm of the primary electrode). Forexample, each neighbor electrode may be located within a pre-selected,or certain, proximity to the primary electrode.

A portion of the first signal may be stored to be used in thecomparative analysis 176 and a portion of each of the one or moresecondary signals 178 may be stored to also be used in the comparativeanalysis. To provide useful data, the portions of the first signal andthe one or more secondary signals may be chosen to include data otherthan an ambient signal (e.g., flat line signal, etc.) and/or noise. Forexample, the portions of the first signal and the one or more secondarysignals may correspond to a fiducial element (e.g., a particular event)within a cardiac waveform (e.g., per cardiac cycle) such as, e.g.,ventricular depolarization, atrial depolarization, ventricularrepolarization, atrial repolarization, etc.

Further, each of the portions of the first signal and the secondarysignals may be window or cropped for a selected, or preset, period oftime such as, e.g., 250 milliseconds. The period of time may be about100 milliseconds (ms) to about 400 ms, such as, e.g., about 100 ms,about 150 ms, about 200 ms, about 250 ms, about 300 ms, about 400 ms,etc. Further, each portion of the first signal and the secondary signalsmay occur (and thus, be recorded) at the same time. For example, theportion of the first signal may be recorded at the exact same time theportion of the secondary signals is recorded. In other words, theportions of the first signal and the secondary signals may be storedover the same time period.

To determine the effectiveness of the primary electrode, the portion ofthe first signal may be compared to the portion of each of the secondarysignals to provide an effectiveness value for each comparison 180. Forexample, if two adjacent neighbor electrodes providing two secondarysignals are utilized, a first comparison may occur between the portionof the first signal and the portion of the first secondary signal toprovide a first effectiveness value, and a second comparison may occurbetween the portion of the first signal and the portion of the secondsecondary signal to provide a second effectiveness value. Each ofeffectiveness values for each primary electrode may represent acorrelation value between the primary electrode and the neighborelectrode. Similar to the methods 130, 140 described herein withreference to FIGS. 5-6, the effectiveness values may be correlationcoefficients (e.g., Pearson correlation coefficients), waveform matchpercentages, etc.

The exemplary method 170 may then determine whether the primaryelectrode is effective by comparing the effectiveness values to athreshold value 182 similar to the threshold values described hereinwith respect to the methods 130, 140 of FIGS. 5-6. In this embodiment,each primary electrode may have multiple effectiveness values since thesignal of the primary electrode may be compared to a secondary signalfrom more than one secondary electrode. If multiple effectiveness valuesare generated, various statistical processes may be used to provide asingle value. For example, the greatest effectiveness value may be used.Further, for example, an average of the effectiveness values may beused. Still further, effectiveness values that are outliers may beexcluded while the remaining effectiveness values may be used.

In at least one embodiment, if one of the effectiveness values isgreater than a threshold value, then the method 170 may determine thatthe primary electrode is effective 182. In other words, a single strongcorrelation between the primary electrode and an adjacent neighborelectrode may indicate that the primary electrode is effective.

Conversely, in at least one embodiment, if all of the effectivenessvalues are less than a threshold value, then the method 170 maydetermine that the primary electrode is ineffective 182. In other words,no strong correlation between the primary electrode and an adjacentneighbor electrode may indicate that the primary electrode isineffective.

The method 170 may be repeated for each electrode of an electrode arrayor IMD until each electrode is determined to be effective orineffective. Further, the method 170 may be performed sequentially withone electrode at a time or in parallel by recording the signal from eachelectrode of a plurality of electrodes at the same time.

Although not shown, the exemplary systems and apparatus described hereinmay provide a display to depict, or show, information with respect tothe effectiveness of the electrodes. For example, a graphicalrepresentation of an array of electrodes may be depicted on the displayand information with respect to the effectiveness of each of theelectrodes may be depicted proximate each of the electrodes. In at leastone embodiment, a graphical map may be generated that includes aplurality of electrodes spatially distributed and an effectivenessvalues for each of the plurality of electrodes depicted proximate theelectrodes. A user may use the graphical map to determine areas of thearray that may not be located, or fitted, properly to the user to createsufficient contact between the electrodes and the tissue of the patient.

Further, similar to the method 156 of FIG. 7, an additionaleffectiveness test for each electrode may be performed or repeated ifmore than a selected percentage of the plurality of electrodes wereidentified as being ineffective. For example, if 50% of the electrodeshad all of their at least one correlation value less than a selectedthreshold value, then the method 170 may repeat or retest the array ofelectrodes. Prior to retesting, a user may re-adjust the array ofelectrodes to, e.g., provide better contact between the electrodes andthe tissue of the patient.

A graph 190 depicting effectiveness values for a plurality of electrodesis shown in FIG. 10. The ineffective electrodes 192 are identifiable onthe graph 190 as having effectiveness values less than the thresholdvalue 194, which, as shown, is 0.8.

Cardiac signals measured, or monitored, from ineffective electrodes aredepicted in FIG. 11 and cardiac signals measured, or monitored, fromeffective electrodes are depicted in FIG. 12. As shown, the signals fromthe ineffective signals appear to not correlate to any pattern orsequence and further appear to depict random noise. The signal from theeffective electrodes appears to correlate to a pattern (e.g., a valley)and appear to depict a portion of a valid cardiac signal.

A distribution of correlation values for a plurality of electrodesevaluated by, e.g., the exemplary methods of FIGS. 6-7 and 9, isdepicted in FIG. 13. As shown in this example, a vast majority of theelectrodes had correlation values between 0.9 and 1.

An exemplary method 200 of identifying an active or effective electrodeusing morphological features is depicted in FIG. 14. In at least oneembodiment, the method 200 may be used prior to the exemplary method 170described herein with reference to FIG. 9 to, e.g., prevent signals fromspatially adjacent electrodes to be compared, or correlated, when one ormore of the spatially adjacent electrodes read, or sense, only a flatline or noise. In at least one embodiment, the method 200 may beperformed on its own to provide an effectiveness value for an active oreffective electrode.

The method 200 includes monitoring a signal using an electrode 202 andanalyzing at least one morphological feature of the signal to determineif the electrode is active (or effective) 204. For example, whether anelectrode is active or effective may be determined by at least one ofthe signal maximum value, minimum value, difference between maximum andminimum value, maximum slope, minimum slope, difference between maximumslope and minimum slope, etc. The morphological feature may be comparedto a threshold value (e.g., greater than or equal to a predefined value,less than or equal to another predefined value, etc.).

For example, features of the signal from one electrode within adepolarization cycle (e.g., amplitude, slope, etc.) may be used to judgeif the value corresponding to those features is within physiologiclimits. More specifically, e.g., ECG signal depolarization amplitudevalue should be within certain physiologic limits such as, e.g., greaterthan or equal to 0.1 mV and less than or equal to 10 mV. The ECG signaldepolarization peak-to-peak amplitude value may be evaluated bycomparing the value to the physiological limits to determine if theelectrode is active (which, e.g., may be useful if multiple spatiallyadjacent electrodes are all recording a flat line). Physiologic limitson signal depolarization amplitude for electrode arrays in contact withcardiac tissue may be much larger, e.g., greater than or equal to 1 mVand less than or equal to 50 mV.

These values or data for various electrodes may be mapped (e.g., mappedto a grid for visualization, mapped to a database for analysis, etc.)and/or compared to identify one or more active and/or effectiveelectrodes.

An exemplary graphical user interface 132 including blood vessel anatomy134 of a patient's heart is shown in FIG. 15 that may be used by a userto navigate an implantable electrode to a region of the patient's heart.The blood vessel anatomy as well as other data such as mechanical motioninformation, etc. of the heart may be captured using the imagingapparatus 120 described herein, which may be configured to image atleast a portion of blood vessel anatomy of the patient's heart andprovide image data used by the computing apparatus 140 to providemechanical motion information or data. The data or information depictedon the blood vessel anatomy of the patient's heart in FIG. 15 may befurther monitored, or gathered, using the electrode apparatus 110described herein.

A user may view and/or use the graphical user interface 132 of FIG. 15to determine, or identify, one or more candidate site regions of thedisplayed portion or region of the patient's heart for implantation ofimplantable electrodes. For example, a user may view mechanical motioninformation, e.g., grey-scaling or color-coding applied to the bloodvessel anatomy in FIG. 15, and identify a candidate site region of thepatient's heart based on the mechanical motion information. For example,a user may identify one or more regions having, e.g., mechanical motiontimes greater than a threshold, having the longest mechanical motiontime, etc.

Another exemplary graphical user interface 132 including a graphicaldepiction of a patient's heart 12 is shown in FIG. 16 that may be usedby a user to navigate an implantable electrode to a region of thepatient's heart. More specifically, a posterior side of a human heart 12is depicted in the graphical user interface 132 of FIG. 16 withsurrogate electrical activation times 136 color-coded, or gray-scaled,across the surface of the heart 12. As used herein, surrogate electricalactivation data (e.g., surrogate electrical activation times, surrogateelectrical activation time maps, etc.) may be defined as datarepresentative of actual, or local, electrical activation data of one ormore regions of the patient's heart. For example, electrical signalsmeasured at the left anterior surface location of a patient's torso maybe representative, or surrogates, of electrical signals of the leftanterior left ventricle region of the patient's heart, electricalsignals measured at the left lateral surface location of a patient'storso may be representative, or surrogates, of electrical signals of theleft lateral left ventricle region of the patient's heart, electricalsignals measured at the left posterolateral surface location of apatient's torso may be representative, or surrogates, of electricalsignals of the posterolateral left ventricle region of the patient'sheart, and electrical signals measured at the posterior surface locationof a patient's torso may be representative, or surrogates, of electricalsignals of the posterior left ventricle region of the patient's heart.

As shown, the posterolateral left ventricle region shows late activation(e.g., about 150 milliseconds). In other embodiments, both a posteriorand anterior side of a human heart may be graphically depicted andoverlaid with electrical activation information. The data or informationdepicted on the patient's heart 12 in FIG. 16 may be further monitored,or gathered, using the electrode apparatus 110 described herein.

The techniques described in this disclosure, including those attributedto the IMD 16, the programmer 24, the computing apparatus 140, and/orvarious constituent components, may be implemented, at least in part, inhardware, software, firmware, or any combination thereof. For example,various aspects of the techniques may be implemented within one or moreprocessors, including one or more microprocessors, DSPs, ASICs, FPGAs,or any other equivalent integrated or discrete logic circuitry, as wellas any combinations of such components, embodied in programmers, such asphysician or patient programmers, stimulators, image processing devices,or other devices. The term “module,” “processor,” or “processingcircuitry” may generally refer to any of the foregoing logic circuitry,alone or in combination with other logic circuitry, or any otherequivalent circuitry.

Such hardware, software, and/or firmware may be implemented within thesame device or within separate devices to support the various operationsand functions described in this disclosure. In addition, any of thedescribed units, modules, or components may be implemented together orseparately as discrete but interoperable logic devices. Depiction ofdifferent features as modules or units is intended to highlightdifferent functional aspects and does not necessarily imply that suchmodules or units must be realized by separate hardware or softwarecomponents. Rather, functionality associated with one or more modules orunits may be performed by separate hardware or software components, orintegrated within common or separate hardware or software components.

When implemented in software, the functionality ascribed to the systems,devices and techniques described in this disclosure may be embodied asinstructions on a computer-readable medium such as RAM, ROM, NVRAM,EEPROM, FLASH memory, magnetic data storage media, optical data storagemedia, or the like. The instructions may be executed by one or moreprocessors to support one or more aspects of the functionality describedin this disclosure.

This disclosure has been provided with reference to illustrativeembodiments and is not meant to be construed in a limiting sense. Asdescribed previously, one skilled in the art will recognize that othervarious illustrative applications may use the techniques as describedherein to take advantage of the beneficial characteristics of theapparatus and methods described herein. Various modifications of theillustrative embodiments, as well as additional embodiments of thedisclosure, will be apparent upon reference to this description.

What is claimed:
 1. A system for use in cardiac therapy comprising: electrode apparatus comprising a plurality of electrodes configured to be located proximate tissue of a patient; display apparatus comprising a graphical user interface, wherein the graphical user interface is configured to graphically depict at least a portion of anatomy of the patient's heart for use in assisting a user in navigating at least one implantable electrode to a region of the patient's heart; and computing apparatus coupled to the electrode apparatus and display apparatus, wherein the computing apparatus is configured to perform an effectiveness test for each electrode of the plurality of electrodes resulting in an effectiveness value for each electrode representative of the effectiveness of the electrode in providing a valid sensing signal from the tissue of the patient, wherein, to perform the effectiveness test for each electrode, the computing apparatus is further configured to: monitor a first signal from the patient using a primary electrode being tested, monitor at least one secondary signal from the patient using at least one neighbor electrode, wherein the at least one neighbor electrode is spatially adjacent to the primary electrode, store a portion of the first signal being monitored using the primary electrode being tested over a time period, store a portion of each of the at least one secondary signal being monitored using the at least one neighbor electrode over the time period, compare the portion of the first signal monitored using the primary electrode being tested to the portion of each of the at least one secondary signal to provide at least one effectiveness value representative of the effectiveness of the same primary electrode being tested in providing a valid sensing signal from the tissue of the patient, and display, on the graphical user interface, information for use in assisting a user in at least one of assessing a patient's cardiac health, evaluating and adjusting cardiac therapy delivered to a patient, and navigating at least one implantable electrode to a region of the patient's heart.
 2. The system of claim 1, wherein each of the at least one effectiveness value for each primary electrode represent a correlation value between the primary electrode and one neighbor electrode.
 3. The system of claim 1, wherein the time period corresponds to ventricular depolarization.
 4. The system of claim 1, wherein the time period is less than or equal to 250 milliseconds.
 5. The system of claim 1, wherein the at least one neighbor electrode is within 3 centimeters from the primary electrode.
 6. The system of claim 1, wherein the effectiveness value comprises a Pearson correlation coefficient.
 7. The system of claim 1, wherein the plurality of electrodes comprises surface electrodes positioned in an array.
 8. The system of claim 1, wherein the effectiveness value comprises a correlation value, and wherein the computing apparatus is further configured to disable any electrode of the plurality of electrodes having all of their at least one correlation value less than or equal to a selected threshold value.
 9. The system of claim 1, wherein the computing apparatus is further configured to perform an additional effectiveness test for each electrode of the plurality of electrodes resulting in at least one additional correlation value for each electrode if more than a selected percentage of the plurality of electrodes had all of their at least one correlation value less than a selected threshold value.
 10. The system of claim 1, wherein the computing apparatus is further configured to generate a graphical map comprising the plurality of electrodes spatially distributed and the effectiveness values of the plurality of electrodes.
 11. The system of claim 1, wherein information for use in assisting a user in at least one of assessing a patient's cardiac health, evaluating and adjusting cardiac therapy delivered to a patient, and navigating at least one implantable electrode to a region of the patient's heart comprises at least a portion of the blood vessel anatomy of the patient's heart.
 12. A method for use in cardiac therapy comprising: monitoring a first signal from a patient using a primary electrode being tested to determine an effectiveness of the primary electrode in providing a valid sensing signal from tissue of the patient; monitoring at least one secondary signal from the patient using at least one neighbor electrode, wherein the at least one neighbor electrode is spatially adjacent to the primary electrode; storing a portion of the first signal being monitored using the primary electrode being tested over a time period; storing a portion of each of the at least one secondary signal being monitored using the at least one neighbor electrode over the time period; comparing the portion of the first signal monitored using the primary electrode being tested to the portion of each of the at least one secondary signal to provide at least one effectiveness value representative of the effectiveness of the same primary electrode being tested in providing a valid sensing signal for sensing cardiac signals from the tissue of the patient; and displaying, on a graphical user interface, information for use in at least one of assessing a patient's cardiac health, evaluating and adjusting cardiac therapy delivered to a patient, and assisting a user in navigating at least one implantable electrode to a region of the patient's heart.
 13. The method of claim 12, wherein each of the at least one effectiveness value for each primary electrode represent a correlation value between the primary electrode and one neighbor electrode.
 14. The method of claim 12, wherein the time period corresponds to ventricular depolarization.
 15. The method of claim 12, wherein the at least one neighbor electrode is within 3 centimeters from the primary electrode.
 16. The method of claim 12, wherein the plurality of electrodes comprises surface electrodes positioned in an array.
 17. The method of claim 12, wherein the effectiveness value comprises a correlation value, and wherein the method further comprises disabling any electrode of the plurality of electrodes having all of their at least one correlation value less than or equal to a selected threshold value.
 18. The method of claim 12, wherein the method further comprises performing an additional effectiveness test for each electrode of the plurality of electrodes resulting in at least one additional correlation value for each electrode if more than a selected percentage of the plurality of electrodes had all of their at least one correlation value less than a selected threshold value.
 19. The method of claim 12, wherein the method further comprises generating a graphical map comprising the plurality of electrodes spatially distributed and the effectiveness values of the plurality of electrodes.
 20. A system for use in cardiac therapy comprising: electrode means for monitoring a first signal from a patient using a primary electrode being tested to determine the effectiveness of the primary electrode in providing a valid sensing signal from tissue of the patient and for monitoring at least one secondary signal from the patient using at least one neighbor electrode, wherein the at least one neighbor electrode is spatially adjacent to the primary electrode; computing means for storing a portion of the first signal being monitored using the primary electrode being tested over a time period, for storing a portion of each of the at least one secondary signal being monitored using the at least one neighbor electrode over the time period, and for comparing the portion of the first signal monitored using the primary electrode being tested to the portion of each of the at least one secondary signal to provide at least one effectiveness value representative of the effectiveness of the same primary electrode being tested in providing a valid sensing signal from the tissue of the patient; and display means for displaying, on a graphical user interface, information for use in at least one of assessing a patient's cardiac health, evaluating and adjusting cardiac therapy delivered to a patient, and assisting a user in navigating at least one implantable electrode to a region of the patient's heart. 